Pressure attenuation device

ABSTRACT

An pressure attenuation device for use in a body can include a balloon comprising an outer wall and defining an interior chamber therein. The balloon can be configured to elastically deform up to at least to an internal pressure of 90 cm H2O. A high vapor pressure media having a vapor pressure of between 155 cm-185 cm H2O at 37 degrees Celsius can be positioned within the interior chamber. The balloon can have a minimum wall thickness of between 0.001 inches-0.00175 inches.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority to U.S. Provisional Application No.62/802,622, filed on Feb. 7, 2019, the entirety of which is herebyincorporated by reference herein for all purposes.

BACKGROUND Field

The present disclosure relates to methods and systems for performingmedical procedures on anatomical structures of the body. Such medicalprocedures may involve, for example, attenuating transient pressurewaves in anatomical structures of the body, for example, by implanting apressure attenuation device in anatomical structure of the body that issubjected to such pressure waves.

Description of the Related Art

Pressure waves are known to propagate through incompressible fluids invarious anatomical structures of the body. These pressure waves may becaused by normally-occurring events within the body, such as a beatingheart, breathing in the lungs, peristalsis actions in the GI tract, andmovement of the muscles of the body. Alternatively, these pressure wavesmay be caused by sudden events, such as coughing, laughing, externaltrauma to the body, and movement of the body relative to gravity. As theelasticity of the surrounding tissues and organs, sometimes referred toas compliance, decreases, the propagation of these pressure wavesincreases. These pressure waves have many undesirable effects rangingfrom discomfort to stress on the organs and tissue to fluid leakage torenal failure to stroke to heart attack to blindness.

Urinary tract disorders, such as frequency, urgency, incontinence, andcystitis, are a widespread problem in the United States and throughoutthe world, affecting people of all ages, both physiologically andpsychologically. Urine is primarily composed of water and is a virtuallyincompressible fluid in the typical pressure ranges that are presentwithin the human bladder. The relationship between the maximum urethralpressure and the intravesical pressure for normal voiding of the bladderis well-defined. During normal voiding, relaxation of the urethra occursbefore the detrusor muscle contracts to cause the intravesical pressureto exceed the urethral pressure.

Intravesical pressure spikes often result from volumetric tissuedisplacement in response to gravity, muscular activity or rapidacceleration. The lack of compliance of the bladder and the urinecontained in the bladder with respect to events of high frequency, highintensity and short wavelength results in minimal fluidic pressureattenuation of the higher frequency pressure wave(s) and results in highintravesical pressures that are directly transmitted to the bladder neckand urethra, which may or may not cause detrusor contractions. Underthese conditions, the urethra may act as a volumetric pressure reliefmechanism, allowing a proportional volume of fluid to escape thebladder, thereby lowering the intravesical pressure to a tolerablelevel. The urethra has a maximum urethral pressure value, and when theintravesical pressure exceeds the maximum urethral pressure, fluid willescape the bladder. Under these conditions, nerve receptors in thebladder and/or bladder neck and/or trigone trigger a detrusorcontraction that may lead to matriculation (frequency) or may subsidewithout matriculation (urgency) or may lead to the intravesical pressureexceeding the maximum urethral pressure resulting in fluid escaping thebladder (stress incontinence).

For the vast majority of patients suffering from problems of urinarytract disorders, such as frequency, urgency, stress and urgeincontinence and cystitis, the cause and/or contributor to bladderdysfunction is a reduction of overall dynamic bladder compliance, asopposed to a reduction of steady-state bladder compliance. Thesepatients may often have bladders that are compliant in steady-stateconditions but that become non-dynamically compliant when subjected toexternal pressure events having a short duration of, for example, lessthan 5 seconds or, in some cases, less than 0.5 seconds. Reduction indynamic compliance of the bladder is often caused by aging, use,distention, childbirth and trauma. In addition, the anatomical structureof the bladder in relation to the diaphragm, stomach, and uterus (forwomen) causes external pressure to be exerted on the bladder duringphysical activities, such as talking, walking, laughing, sitting,moving, turning, and rolling over. For a patient suffering from stressincontinence due to lack of dynamic compliance in the bladder, when theintravesical pressure exceeds the maximum urethral pressure, leakageoccurs.

In light of the foregoing, a number of attempts have been made to combaturinary tract disorders. One such attempt has been to implant acompressible, pressure-attenuating device in the bladder in order tolower the intravesical pressure. This approach is disclosed, forexample, in the following documents, all of which are incorporatedherein by reference: U.S. Pat. No. 6,682,473, Matsuura et al., issuedJan. 27, 2004; U.S. Pat. No. 7,074,178, Connors et al., issued Jul. 11,2006; and U.S. Patent Application Publication No. 2010/0222802,Gillespie, Jr. et al., published Sep. 2, 2010. According to one aspectof the foregoing approach, a compressible device is inserted, in acompacted state, into the bladder of a patient through the patient'surethra, and, then, once in the bladder, the compressible device isexpanded, for example, by inflation with atmospheric air. A deliverysystem may be used to deliver the compressible device through theurethra and into the bladder and also may be used to expand thecompressible device from its compacted state to its expanded state andto deploy the compressible device, once expanded, from the deliverysystem. If removal or replacement of the compressible device is desired,a removal system may be used to remove the compressible device from thebladder through the urethra.

SUMMARY

The systems, methods and devices of this disclosure each have severalinnovative aspects, no single one of which is solely responsible for thedesirable attributes disclosed herein.

In an aspect, the present disclosure improves upon prior pressureattenuation devices for use in the bladder. Accordingly, it is an objectof certain embodiments of the disclosure to provide a method and systemfor performing a medical procedure on an anatomical structure, such as abladder, of a body. The medical procedure may be performed, for example,to attenuate transient pressure waves in the anatomical structure andmay involve, for example, implanting a pressure attenuation device inthe anatomical structure, such as a bladder, subject to such pressurewaves. Such a method and system may be used in, but is not limited touse in, treating urinary tract disorders.

Certain embodiments comprise a method of treating a condition affectingthe bladder. The method can include the steps of implanting a pressureattenuation device into a human or animal body. The condition affectingthe bladder can comprise: urinary incontinence, urinary tract cancer, aninfection affecting the bladder, or an inflammatory, condition affectingthe bladder.

In certain embodiments, a pressure attenuation device for use in a bodycan include a balloon comprising an outer wall and defining an interiorchamber therein. The outer wall of the balloon can have a minimum wallthickness of between 0.001 inches and 0.00175 inches. The balloon can beconfigured to elastically deform up to at least to an internal pressureof 90 cm H₂O. In some embodiments, the pressure attenuation device canalso include one or more of the following features in any combination:(a) a high vapor pressure media having a vapor pressure of between 155cm H₂O-185 cm H₂O at 37 degrees Celsius; (b) a high vapor pressure mediamedia having a vapor pressure of between 155 cm H₂O-165 cm H₂O at 37degrees Celsius; (c) wherein the high vapor pressure media is positionedwithin the interior chamber; (d) wherein the high vapor pressure mediacomprises a PFC; (e) wherein the balloon elastically deforms andincreases in volume by at least 10% but less than 90% when the internalpressure within the balloon is increased from 2.5 cm H₂O to 90 cm H₂O;(f) wherein the balloon elastically deforms and increases in volume byat least 75% but less than 90% when the internal pressure within theballoon is increased from 2.5 cm H₂O to 90 cm H₂O; (g) wherein theballoon elastically deforms to at least an internal pressure of 120 cmH₂O; (h) wherein the balloon has a natural volume of between 1 and 180cc, between 10 and 60 cc, between 24 ml and 40 ml, or between 25 ml and29 ml; (i) wherein the balloon elastically deforms between internalpressures of 2.5 cm H₂O to 90 cm H₂O for at least 15 cycles; (j) whereinthe balloon elastically deforms between internal pressures of 2.5 cm H₂Oto 90 cm H₂O for at least 25 cycles; (k) wherein the balloon elasticallydeforms between internal pressures of 2.5 cm H₂O to 90 cm H₂O for atleast 50 cycles; and/or (1) wherein the balloon elastically deformsbetween internal pressures of 2.5 cm H₂O to 90 cm H₂O for at least 100cycles.

In certain embodiments, a pressure attenuation device for use in a bodycan include a balloon comprising an outer wall and defining an interiorchamber therein. The device can include a high vapor pressure media. Theballoon can be configured to deform elastically at least up to aninternal pressure within the chamber of 90 cm H₂O.

In certain embodiments, a pressure attenuation device can include aballoon comprising an outer wall and defining an interior chambertherein. The balloon can be configured to elastically deform up to atleast to an internal pressure of 90 cm H₂O. A high vapor pressure mediahaving a vapor pressure of between 155 cm-185 cm H₂O at 37 degreesCelsius can be within the balloon. In some embodiments, the pressureattenuation device can also include one or more of the followingfeatures in any combination: (a) wherein the high vapor pressure mediahas a vapor pressure of between 155 cm H₂O-165 cm H₂O at 37 degreesCelsius; (b) wherein the high vapor pressure media is positioned withinthe interior chamber (c) wherein the high vapor pressure media comprisesa PFC; (d) wherein the balloon elastically deforms between internalpressures of 2.5 cm H₂O to 90 cm H₂O for at least 15 cycles, 25 cycles,50 cycles or 100 cycles; and/or (e) wherein the balloon has a naturalvolume of between 1 and 180 cc, between 10 and 60 cc, between 24 ml and40 ml, or between 25 ml and 29 ml.

In certain embodiments, a pressure attenuation device for use in a bodyincludes a balloon comprising an outer wall and defining an interiorchamber therein. The balloon can be configured to elastically deform andincrease in volume by at least 50% but less than 190% when an internalpressure within the balloon is increased from 2.5 cm H₂O to 90 cm H₂O.In some embodiments, the pressure attenuation device can also includeone or more of the following features in any combination: (a) whereinthe balloon is configured to elastically deform and increase in volumeby at least 65% but less than 100% when a pressure within the balloon isincreased from 2.5 cm H₂O to 90 cm H₂O; (b) wherein the balloon isconfigured to elastically deform and increase in volume by at least 75%but less than 90% when a pressure within the balloon is increased from2.5 cm H₂O to 90 cm H₂O; (c) wherein the balloon is configured toelastically deform and increase in volume by at least 20% but less than150% when a pressure within the balloon is increased from 2.5 cm H₂O to70 cm H₂O; (d) wherein the balloon is configured to elastically deformand increase in volume by at least 30% but less than 100% when apressure within the balloon is increased from 2.5 cm H₂O to 70 cm H20;(e) wherein the balloon is configured to elastically deform and increasein volume by at least 45% but less than 60% when a pressure within theballoon is increased from 2.5 cm H₂O to 70 cm H₂O; (f) wherein theballoon is configured to elastically deform and increase in volume by atleast 10% but less than 45% when a pressure within the balloon isincreased from 2.5 cm H₂O to 40 cm H₂O; (g) wherein the balloon isconfigured to elastically deform and increase in volume by at least 18%but less than 30% when a pressure within the balloon is increased from2.5 cm H₂O to 40 cm H₂O; (h) wherein the balloon is configured toelastically deform and increase in volume by at least 19% but less than27% when a pressure within the balloon is increased from 2.5 cm H₂O to40 cm H₂O; (i) comprising a high vapor pressure media having a vaporpressure of between 155 cm H₂O-185 cm H₂O at 37 degrees Celsius; (j)comprising a high vapor pressure media having a vapor pressure ofbetween 155 cm H₂O-165 cm H₂O at 37 degrees Celsius; (k) wherein thehigh vapor pressure media is positioned within the interior chamber; (l)wherein the high vapor pressure media comprises a PFC; (m) wherein theballoon elastically deforms between internal pressures of 2.5 cm H₂O to90 cm H₂O for at least 15 cycles, 25 cycles, 50 cycles or 100 cycles;(n) wherein the balloon has a natural volume of between 1 and 180 cc,between 10 and 60 cc, between 24 ml and 40 ml, or between 25 ml and 29ml; and/or (o) wherein the balloon has a minimum wall thickness ofbetween 0.001 inches and 0.00175 inches.

In several embodiments, a pressure attenuation device for use in a bodycomprise a balloon comprising an outer wall and defining an interiorchamber therein; and a high vapor pressure media. The balloon isconfigured to deform elastically at least up to an internal pressurewithin the chamber of 90 cm H20. In some embodiments, the pressureattenuation device can also include one or more of the followingfeatures in any combination: (a) wherein the balloon elastically deformsbetween internal pressures of 2.5 cm H₂O to 90 cm H2O for at least 15cycles, 25 cycles, 50 cycles or 100 cycles; (b) wherein the balloon isconfigured to deform elastically at least up to an internal pressurewithin the chamber of 100 cm H₂O; (c) wherein the balloon elasticallydeforms between internal pressures of 2.5 cm H₂O to 100 cm H2O for atleast 15 cycles, 25 cycles, 50 cycles or 100 cycles; (d) wherein theballoon is configured to deform elastically at least up to an internalpressure within the chamber of 120 cm H₂O; (e) wherein the balloonelastically deforms between internal pressures of 2.5 cm H₂O to 120 cmH₂O for at least 15 cycles, 25 cycles, 50 cycles or 100 cycles; (f)wherein the balloon has a natural volume of between 1 and 180 cc,between 10 and 60 cc, between 24 ml and 40 ml, or between 25 ml and 29ml; (g) wherein the balloon has a minimum wall thickness of between0.001 inches-and 0.00175 inches; (h) wherein the high vapor pressuremedia has a vapor pressure of between 155 cm H₂O-185 cm H₂O at 37degrees Celsius; (i) wherein the high vapor pressure media has a vaporpressure of between 155 cm H₂O-165 cm H₂O at 37 degrees Celsius; (j)wherein the high vapor pressure media is positioned within the interiorchamber; (k) wherein the high vapor pressure media comprises a PFC;and/or (l) wherein the high vapor pressure media comprises a liquid at37 degrees Celsius

In certain embodiments, a pressure attenuation device comprises one ormore features of the foregoing description. In certain embodiments, apressure attenuation device comprises one or more features of theforegoing description and is configured to be placed within the bladderof a human.

Certain embodiments include a method of treating urinary incontinence ina human or animal body comprising implanting a pressure attenuationdevice comprising one or more features of the foregoing descriptionwithin a bladder of the human or animal body and inflating the pressureattenuation device while in the bladder. In certain embodiments, themethod also include removing the device from the bladder.

Certain embodiments include a pressure attenuation device comprising oneor more features of the foregoing description configured to be implantedwithin a bladder of a human.

Certain embodiments include a pressure attenuation device comprising oneor more features of the foregoing description configured to be implantedwithin a bladder of a human in an uninflated state and then inflatedwithin the bladder.

Certain embodiments include a pressure attenuation device comprising oneor more features of the foregoing description wherein the ballooncomprises a bulb portion and a tail portion.

Certain embodiments include a pressure attenuation device comprising oneor more features of the foregoing description wherein the balloon isseamless.

Further features and advantages will become apparent to those of skillin the art in view of the detailed description of preferred embodimentswhich follows, when considered together with the attached drawings andclaims.

BRIEF DESCRIPTION OF THE DRAWINGS

In order to better understand the disclosure and to see how it may becarried out in practice, some preferred embodiments are next described,by way of non-limiting examples only, with reference to the accompanyingdrawings, in which like reference numerals denote corresponding thoughnot necessarily identical features consistently throughout theembodiments in the attached drawings.

FIG. 1 illustrates maximum urethral pressure against intravesicalpressure during normal voiding.

FIG. 2 illustrates the intravesical pressure exceeding the maximumurethral pressure in a noncompliant bladder.

FIG. 3 illustrates an intravesical pressure spike exceeding the maximumurethral pressure during stress incontinence.

FIG. 4A illustrates the relationship between intravesical pressure anddetrusor pressure during cough-induced urgency or frequency.

FIG. 4B illustrates the relationship between intravesical pressure anddetrusor pressure during non-cough-induced urgency or frequency.

FIGS. 5A through 5C are perspective views of a pressure attenuationdevice in an inflated state, the fluids within the inflated device notbeing shown.

FIG. 6 is a fragmentary section view of the pressure attenuation deviceof FIGS. 5A through 5C.

FIG. 7 is a top view of the valve shown in FIGS. 5A through 5C.

FIG. 8 is a flowchart, schematically illustrating one method ofmanufacturing the pressure attenuation device of FIGS. 5A through 5C.

FIGS. 9A through 9D are section views, illustrating parts of certainsteps of the method shown in FIG. 8.

FIG. 10A is a schematic top plan view of a pressure attenuation device.

FIG. 10B is a side elevational view of FIG. 10A.

FIGS. 11A-11D present graphs of attenuation/pressure reduction vs. timefor various pressure attenuation device air volumes.

FIGS. 12A-12D show pressure vs. time curves generated by a bench topbladder simulator.

FIG. 13A illustrates a bladder experiencing pressure which causes urineleakage.

FIG. 13B shows the bladder of FIG. 13A with pressure attenuation devicethat absorbs the pressure so that there is no urine leakage.

FIG. 14 charts the pressure within a pressure attenuation device versesthe volume of the pressure attenuation device.

FIG. 15 shows a graph of gas volume versus time for potential balloonloading scenarios.

FIG. 16 shows an attenuation PV curve for an embodiment of pressureattenuation device.

FIG. 17 illustrates P/V curves and elasticity of the balloon accordingcertain embodiments of a pressure attenuation devices.

FIGS. 18A-B shows an embodiment of a delivery device that may be used todeliver a pressure-attenuating device to the target body area.

FIG. 19 shows an embodiment of a sterilizable kit comprising certaincomponents of a delivery device.

FIG. 20 shows an embodiment of a pressure-attenuating device in adeflated, flattened state.

FIGS. 21-21D shows a flow chart and corresponding illustrations of howan embodiment of the balloon can be delivered according to certainembodiments.

FIG. 22 shows an embodiment of a removal device.

FIGS. 23A-23D, FIGS. 24A-24D, and FIGS. 25A-B show embodiments of thejaws of an removal device.

FIGS. 26-26D shows a flow chart and corresponding illustrations of howan embodiment of the balloon can be removed according to certainembodiments.

DETAILED DESCRIPTION

Medical devices, methods, and apparatuses related thereto for use withinthe body are disclosed. The medical devices can include pressurizedtherapeutic devices, implants, implant delivery devices, implantretrieval devices, expandable membrane enclosures or balloons, sponges,attenuators, space occupying members, space creating devices, drugdelivery devices, data collection devices, nerve stimulation devices,wave producing devices, vibration producing devices, pressure sensingdevices, chemical sensing devices, volume sensing devices, and/ortherapeutic devices. The medical devices can be used for many purposesand in many places within the body including, but not limited to thefollowing systems of the human body: cardiovascular, pulmonary,renal/urological, gastrointestinal, hepatic/biliary, gynecological,neurological, musculoskeletal, otorhinolaryngological and ophthalmic, aswell as in and around organs of the body and in intra- and inter-organspace. In particular, in many embodiments disclosed herein, the medicaldevice is a pressure attenuation device which is configured to be placedwithin a patient's bladder. However, it should be appreciated thatcertain embodiments, aspects, and features of the pressure attenuationdevices disclosed herein can find utility in other places in the body asoutlined above and can be used as implants and medical devices that arenot used for pressure attenuation and/or for pressure attenuation withinthe bladder and/or are used to provide other therapeutic benefits.

Embodiments of devices for treating one or more conditions of thebladder including devices that can be used for attenuating transientpressure waves propagating through the bladder, e.g., from coughing orlaughing, to reduce and/or eliminate pressure spike-related incontinenceare disclosed in one or more of U.S. Pat. Nos. 7,470,228 (Dkt. No.SOLACE.4CP1C1), 7,074,178 (Dkt. No. SOLACE.4CP1C2), 7,540,876 (Dkt. No.SOLACE.012A), 8,574,146 (Dkt. No. SOLACE.017A), 8,894,563 (Dkt. No.SOLACE.023A) and U.S. Publication No. 2015/0216644 (Dkt. No.SOLACE.023NP). The entire contents of all of the above patents andpatent publications are incorporated by reference herein for allpurposes and are to be considered a part of this specification.

FIGS. 1-4 illustrate certain graphs of physiologic response to pressure,e.g., bladder response to transient pressure waves. FIGS. 5A-10Billustrate structural features which can be included in certainembodiments of a pressure attenuation device as disclosed herein. FIGS.11A-12D illustrate graphs of various responses to pressure waves,including the response of a bladder, e.g., a model bladder, to transientpressure waves with and without a pressure attenuation device. FIGS.13A-13B illustrates a cross section of a bladder with and without apressure attenuation device which in certain embodiments can beconfigured according to certain embodiments disclosed herein. FIG. 14illustrates a pressure versus volume curve for certain embodiments apressure attenuation device disclosed herein, e.g., the pressureattenuation device's volumetric response to increases in interiorpressure according to certain embodiments.

In one particular aspect, the disclosure relates generally to the fieldof urology and gynecology, and in particular to the treatment ofdisorders of the urinary tract caused by sudden fluctuations ofintravesical pressure. More specifically, in this aspect methods anddevices are provided for the diagnosis and treatment of urinarydisorders such as incontinence, urgency, frequency, interstitialcystitis, irritable bladder syndrome, and neurogenic bladders.

Various embodiments of the pressure attenuation device can maintain agiven pressure and or volume over time, despite gaseous exchange, areprovided. Other embodiments can inflate or deflate over a given timeperiod. Further embodiments can provide a constant force against, withinor between a tissue, vessel, organ, or body cavity. Certain embodimentscan be designed to maintain inflation in oxygen depleted environments.

Various instruments and implants are disclosed herein for theimplantation of pressure attenuation device devices within the bladdervia the urethra, open surgery, or percutaneously through the abdomen,back, vagina, bowel, rectum, or perineum. Certain embodiments of theimplantable medical device can comprise one or more expandable membraneenclosures or balloon, sponge, attenuator, space occupying member, drugdelivery device, data collection device, nerve stimulation device, waveproducing device, vibration producing device, pressure sensing device,chemical sensing device, volume sensing device, or a therapeutic device.From this disclosure it will be appreciated that, although the examplesprovided deal primarily with intravesical applications, the methods anddevices disclosed herein can be used to provide treatment at sitesadjacent the bladder or between layers of bladder tissue. Further, thedevices and methods herein can be used or applied within or proximal toother organs and sites in the body such as the heart, lung, cranium,cardiovascular system, breasts, abdominal area or cavity, eye,testicles, intestines, stomach, or other organs or tissues.

Some embodiments are directed to methods and apparatuses for measuringand/or attenuating and/or baffling transient pressure waves inrelatively incompressible materials in organs of the body. Illustrativeembodiments discussed herein relate generally to the fields of urologyand gynecology, and in particular to the treatment of disorders of theurinary tract exacerbated by sudden fluctuations in intravesicalpressure. However, the devices and methods are not limited to the fieldsof urology and gynecology and methods and apparatuses of embodimentsdisclosed herein can be used in other organs of the body, as well, toattenuate and/or baffle pressure transients or reversibly occupy intra-or inter-organ space.

Certain embodiments dampen transient intravesical pressure includingpressure spikes experienced by the urinary tract. During a transientpressure event, the bladder becomes a relatively non-compliantenvironment due to a number of factors including the pelvic skeletalstructure, the compressive loads of contracting tissues bounding thebladder, the decreased compliance of the musculature, or theincompressible behavior of urine, nerve, or connective tissue of thebladder. Factors contributing to the reduced compliance of the bladderare aging, anatomic abnormalities, or trauma to the structures of thepelvis and abdomen.

Urine is primarily composed of water and is virtually incompressible inthe typical pressure ranges present within the human bladder. Therelationship between the maximum urethral pressure and the intravesicalpressure for normal voiding of the bladder is well defined. Withreference to FIG. 1, relaxation of the urethra occurs before thedetrusor muscle contracts to cause the intravesical pressure 320 toexceed the urethral pressure 322 during normal voiding. The pressuresdiscussed herein are gauge or relative pressures except where absolutepressures and/or atmospheric pressures are specifically mentioned.

The bladder serves two mechanical functions: 1) low-pressure storage and2) high-pressure voiding. During the storage or filling phase, thebladder receives urine from the kidneys. Compliance of the bladder isdefined as the ratio of the change in volume to the change in pressure,and the static compliance of the bladder is measured during a typicalurodynamic evaluation. The static compliance index is measured byfilling the bladder to cystometric capacity and allowing the pressuresto equilibrate for a time period of approximately sixty seconds. Thestatic compliance index is calculated by dividing the bladder capacityby the detrusor pressure at the end of filling. A normal bladder willtypically exhibit static compliance between 15 and 30 ml/cm H₂O. A lowstatic compliance bladder typically will have a compliance index of lessthan 10 ml/cm H₂O. With reference to FIG. 2 which illustrates differentpressures for a non-compliant bladder, a low static compliance bladdertypically is poorly distensible and has a high end-filling pressure. Theintravesical pressure 320 increases to higher levels to exceed themaximum urethral pressure 324. The steady state or static compliance ofthe bladder is used to diagnose patients with neuropathic problems suchas damage to the lower motor neurons, upper motor neurons, or multiplesclerosis. In addition, the steady state compliance of the bladder isalso used, in some cases, to attempt to diagnose problems ofincontinence, including urgency, frequency, and cystitis.

In general, intravesical pressure spikes result from volumetric tissuedisplacement in response to gravity, muscular activity, or rapidacceleration. The lack of compliance of the bladder and the urinecontained in the bladder with respect to events of high frequency resultin minimal fluidic pressure attenuation of the higher frequency pressurewave(s) and results in high intravesical pressures that are directlytransmitted to the bladder neck and urethra, which may or may not causedetrusor contractions. Under these conditions, the urethra can act as avolumetric pressure relief mechanism allowing a proportional volume offluid to escape the bladder, to lower the intravesical pressure to atolerable level. The urethra has a maximum urethral pressure value, andwhen the intravesical pressure exceeds the maximum urethral pressure,fluid will escape the bladder. Under these conditions, nerve receptorsin the bladder and/or bladder neck and/or trigone area trigger adetrusor contraction that can lead to micturition (frequency) or cansubside without micturition (urgency) or can lead to the intravesicalpressure exceeding the maximum urethral pressure resulting in fluidescaping the bladder (incontinence). Under these conditions, waveshitting and/or expanding the bladder wall can cause a patient withcystitis to exhibit significant pain.

Incontinence is common in males who have undergone radicalprostatectomy, particularly where the sphincter has been compromised. Inthese patients, attenuation in the bladder reduces the intravesical peakpressures, resulting in less urine leakage. The attenuation requirementsin these patients can include short duration pressure changes—such as,for example, 50 to 400 ms—and long duration pressure changes—such as,for example, greater than 500 ms—depending on the magnitude of damage tothe urinary sphincter.

An aspect of certain embodiments of the present disclosure is therecognition that for the vast majority of patients suffering fromproblems of urinary tract disorders such as frequency, urgency, stress,and urge incontinence and cystitis, the cause and/or contributor to thebladder dysfunction is a reduction of overall dynamic bladder compliancerather than steady state bladder compliance. These patients can oftenhave bladders that are compliant in steady state conditions, but havebecome non dynamically compliant when subjected to external pressureevents having a short duration of, for example, less than 5 seconds orin some cases less than 2 seconds or even less than 0.01 seconds.Reduction in dynamic compliance of the bladder is often caused by someof the same conditions as reduction of steady state compliance includingaging, use, distention, childbirth, and trauma. The anatomical structureof the bladder in relation to the diaphragm, viscera, and uterus (forwomen) causes external pressure to be exerted on the bladder duringtalking, walking, laughing, sitting, moving, turning, and rolling over.

The relationship between intravesical pressure 320 and the maximumurethral pressure 324 for a patient suffering from stress incontinencedue to lack of dynamic compliance in the bladder is illustrated in FIG.3. When the patient coughs (or some other stress event occurs), a spike326 will occur in the intravesical pressure. Intravesical pressurespikes in excess of 120 cm H₂O have been urodynamically recorded duringcoughing, jumping, laughing, or sneezing. When the intravesical pressureexceeds the maximum urethral pressure value, leakage occurs. In order toretain urine during an intravesical pressure spike, the urinaryretention resistance of the continent individual needs to exceed thepressure spike. Urinary retention resistance can be simplified as thesum total of the outflow resistance contributions of the urethra,bladder neck, and meatus. In female patients, it is generally believedthat the largest resistance component is provided by the urethra. Onemeasure of urinary resistance is the urodynamic measurement of urethralleak pressure. The incontinent individual typically has a urethral leakpressure less than 80 cm H₂O. The decline of adequate urinary retentionresistance has been attributed to a number of factors including reducedblood flow in the pelvic area, decreased tissue elasticity, neurologicaldisorders, deterioration of urethral muscle tone, and tissue trauma.

In practice, the urethral leak point pressure is determined by fillingthe bladder with a known amount of fluid and measuring the intravesicaland abdominal pressures when there is a visible leak from the urethrawhile the patient is “bearing-down” (valsalva). With an attenuationdevice in the bladder, the measured intravesical leak point pressuretypically increases due to the absorption of some the abdominal energyby the attenuation device. In this case, the patient has to push harderto achieve the same intravesical pressure. Since the abdominal musclesand muscles surrounding the urethra both contract simultaneously duringa valsalva maneuver, the measured intravesical leak point pressure andurethral resistance increases when the attenuation device is in thebladder.

Urinary disorders, such as urgency, frequency, otherwise known asoveractive bladder, and interstitial cystitis are caused or exacerbatedwhen rapid pressure increases or rapid volume increases or otherirritable conditions within the bladder cause motor neurons to sendsignals to the brain to begin the cascade of events necessary forurination. External pressure exerted on the bladder can result in adetrusor contraction that can result in urgency, frequency, orincontinence. See FIGS. 4A (cough-induced urgency/frequency) and 4B(non-cough-induced urgency/frequency). With reference to FIG. 4A, acoughing event 328 induces increased intravesical pressure 320 whichresults in increased detrusor pressure 330. An increase in the detrusorpressure 330 generally is associated with increased urgency, frequency,or incontinence. Urinary disorders such as interstitial cystitis orirritable bladder conditions are a chronic inflammatory condition of thebladder wall, which includes symptoms of urgency and/or frequency inaddition to pain. Therefore, the problem of a pressure spike in thefunctionally noncompliant bladder can be further exacerbated by a nearlysimultaneous contraction of the bladder and a relaxation of the urethra.

Some embodiments provide methods and devices for treating and/orcompensating for reduced dynamic compliance of the bladder. In someembodiments, an attenuation device having a compressible element isplaced within the human urinary bladder in a manner that allows thecompressible element to act as a pressure attenuator to attenuatetransient pressure events. The term attenuator or pressure attenuationdevice can refer generally to devices that attenuate pressure, force, orenergy by dissipating or dampening the pressure, force, or energy.Gases, such as atmospheric air, carbon dioxide, nitrogen, and certainperfluorocarbons (PFC) are very compressible in the pressure rangestypically encountered in the human bladder, and can be used inattenuation devices inserted in the bladder. Furthermore, when comparedto the tissues encompassing urine, gases are significantly morecompliant than the immediate environment. The addition of a volume ofgas acts as a low rate spring in series with the native fluidic circuitof the urinary tract.

In accordance with some embodiments, a pressure attenuation device isplaced within the human urinary bladder. The attenuation device can be apressurized container. The container can take many forms including asphere. The pressure attenuation device can be untethered in the bladderand can remain in the bladder for between several hours and one year,between one week and six months, or between one day and three months. Incertain embodiments, the pressure attenuation device can include aballoon with a relaxed (unstretched or natural) volume of between 1 and500 cc, more preferably between 10 and 180 cc, and, more preferablystill, between 25 and 60 cc, and, more preferably still, between 25 and29 cc. In certain embodiments, two or more discreet pressure attenuationdevices are used. In such embodiments, the sum of the volumes of thepressure attenuation devices can equal the desired uncompresseddisplacement.

The pressure attenuation device can be a unitary component but can, incertain embodiments, be comprised of two or more subcomponents. Thepressure attenuation device can be made with or without a seam. Thepressure attenuation device can comprise a balloon having an averagewall thickness between 0.0003 and 0.005 inches in certain embodiments,or between 0.0008 and 0.0025 inches in certain embodiments orbetween.002 and 0.0035 inches in certain embodiments, and between 0.001and 0.00175 inches in certain embodiments. In some embodiments, theminimum wall thickness of the outer wall of the balloon is between 0008and 0.00325 inches in certain embodiments, between 0.002 and 0.0035inches in certain embodiments, and between 0.001 and 0.00175 inches incertain embodiments. In some embodiments, the minimum wall thicknesslocation of the balloon is at the equator of the balloon. In someembodiments, the equator of a balloon is the widest diameter of theballoon along an axis that is perpendicular to the longitudinal axis ofthe balloon. In some embodiments, the equator of a balloon is the widestdiameter along an axis that is perpendicular to the transverse axis ofthe balloon. In other embodiments, the balloon wall thickness could bevaried from these ranges. In some embodiments described herein, pressureattenuation device is free-floating in the bladder as has beendescribed. In other embodiments, the pressure attenuation devices couldbe surgically affixed to the bladder wall through the use of suture,staples and other accepted methods, or placed submucosally orintramuscularly within the bladder wall. Other embodiments could alsoinclude pressure attenuation devices with programmable, variable, andadjustable buoyancy by using ballasting, specific inflation/deflationsolutions, alternative materials of construction, or by other means.

Pressure Attenuation Device

A pressure attenuation device (also referred to herein as “device”)comprising a balloon can be placed within a body, such as the bladder.The balloon can form a compressible element that can act as a pressureattenuator to attenuate transient pressure events. In certainembodiments, gases, such as atmospheric air, carbon dioxide, nitrogen,and certain perfluorocarbons (PFC), can be used to inflate the pressureattenuation device and can act as a low or variable rate spring inseries with the native fluidic circuit of the urinary tract. Thepressure attenuation device can take many forms including a sphere, someexamples of which are outlined herein.

In some embodiments, the balloon of the pressure attenuation device caninclude outer wall that defines a interior chamber within the outerwall. The device can also include a valve that can allow for theaddition or removal of substances from within the balloon. In someembodiments, an pressure attenuation device for use in a body comprisesa balloon having an outer wall defining an interior chamber therein. Theballoon can be defined by a number of parameters, including, but notlimited to, a natural volume, a maximum volume, wall material, wallstiffness, and wall thickness. Certain embodiments of constructing theballoon and pressure attenuation device will be described below FIGS.5A-10B along with certain structural aspects of the balloon and pressureattenuation device, which can be utilized in the embodiments describedherein.

Additional embodiments of an implantable pressure attenuation device aredescribed in U.S. Pat. No. 6,682,473, incorporated by reference herein.See for example, FIGS. 5, 5A, 7A-C, 8A-E, 13-25, and 27-31, and theaccompanying discussion, including at columns 9-12, 13-14, 17-20, and21-24. See also the disclosure from U.S. Pat. No. 6,976,950,incorporated by reference herein, as well as, FIGS. 32A-33C, 36-38,47A-C, 49 and the accompanying discussion, including at columns 15-18,30-35, and 39-40.

U.S. Patent Application Publication No. 2010/0222802 (now U.S. Pat. No.8,574,146) incorporated by reference herein discloses still additionalembodiments of implantable pressure attenuation devices. See forexample, FIGS. 5-5N, 8A-8B, 10A, 11C, 34A-35D, 37A-37B, 38A-51C, and theaccompanying discussion, including paragraphs [0127]-[0152],[0167]-[0168], [0174], [0177], [0233]-[0242], [0354]-[0438], and[0466]-[0475].

Referring now to FIGS. 5(A) through 6, various embodiments of a pressureattenuation device 17 (also referred to herein as “device 17” or“device”) will now be described. As shown in these figures, in theillustrated embodiment, the device 17 can comprise a balloon 1711 and avalve 1713. The valve 1713 can serve to regulate the flow of fluid intoand out of the balloon 1711. The balloon 1711 can comprise an outer wall1709 that can define an interior chamber 1707 (see FIG. 6).

The balloon 1711 can be made of flexible material such as an elastomericmaterial. In some embodiments, the balloon 1711 e.g., the outer wall1709 (all or most of the outer wall 1709) of the pressure-attenuatingdevice 17 can be constructed out of flexible material such as anelastomeric material. Such elastomeric materials for the balloon 1711and the outer wall 1709 include, but are not limited to, polyurethane,polyester, polyamide, polyester copolymer, polyamide copolymer,polyethylene, polypropylene, polystyrene/polybutadiene copolymer,thermoplastic polyurethanes, and combinations thereof.

Examples of polyesters include polyethylene terephthalate (PET) polymersand polybutylene terephthalate (PBT) polymers. Examples of commerciallyavailable PET polymers include the Selar PT family of PET polymers(e.g., Selar PT8307, Selar PT4274, Selar PTX280), which are commerciallyavailable from E. I. DuPont de Nemours (Wilmington, Del.), the Cleartuffamily of PET polymers (e.g., Cleartuf 8006), which are commerciallyavailable from M&G Polymers (Apple Grove, W. Va.), the Traytuf family ofPET polymers (e.g., Traytuf 1006), which are commercially available fromthe Shell Chemical Company (Houston, Tex.), and the Melinar family ofPET polymers (e.g., Melinar 5922C), which are commercially availablefrom E. I. DuPont de Nemours (Wilmington, Del.).

Examples of commercially available PBT polymers include the Celanexfamily of polymers, commercially available from Ticona (Summit, N.J.),the Riteflex family of polymers, commercially available from Ticona(Summit, N.J.), the Hytrel family of PBT copolymers (e.g., Hytrel 5556,Hytrel 7246, Hytrel 4056), commercially available from E. I. DuPont deNemours (Wilmington, Del.), and the Arnitel family of PBT copolymers(e.g., Arnitel EM630), commercially available from DSM (Erionspilla,Ind.).

Examples of polyamides include the nylon family of polymers, such as,for example, aliphatic nylons and aromatic nylons. Examples of aliphaticnylons include nylon 12, nylon 6, nylon 6/10, nylon 6/12 and nylon 11.Nylon 12 is commercially available from, for example, Atofina(Philadelphia, Pa.). Nylon 12 is also commercially available as theGrilamid family of polymers from EMS (Sumter, SC.) and as the Vestamidfamily of polymers from Daicel-Degussa Ltd. Nylon 6 is commerciallyavailable from, for example, HoneyWell (MorristoWn, N.J Nylon 6/ 10 iscommercially available from, for example, BASF (Mount Olive, N.J.).Nylon 6/12 is commercially available from, for example, Ashley Polymers(Cranford, N.J.). Nylon 11 is commercially available from EMS (Sumter,S.C.).

Examples of aromatic nylons include the Grivory family of polymers(commercially available from EMS (Sumter, S.C.)), nylon MXD-6 polymers(commercially available from Mitsubishi Gas Chemical (Tokyo, Japan)),and the Trogamid family of polymers (commercially available from DegussaAG (Germany).

Additional examples of polyamides include polyether block polyamidecopolymers (commercially available, for example, as the Pebax family ofpolymers (e.g., Pebax 2533, Pebax 3533, Pebax 4033, Pebax, 5533, Pebax6033, Pebax 7033, Pebax 7233) from Atofina (Philadelphia, Pa.)).

When inflated, the balloon 1711 can comprise a generally spherical bulbportion 1714 and an inverted tubular tail portion 1717 extending intobulb portion 1714, tail portion 1717 terminating in an opening 1719(FIG. 6). The balloon can contain an inflation media also referred toherein as a pressure media. The inflation media 1705 can contain a highvapor pressure media such that the balloon can contain the high vaporpressure media 1705. In some embodiments, the balloon can be inflatedwith other gases in addition to the high vapor pressure media. In suchembodiments, the inflation media can contain other gasses in addition tothe high vapor pressure media such as air, nitrogen, oxygen, argon,hydrogen, oxygen, helium, carbon dioxide, neon, krypton, xenon, radon,and etc. In the illustrated embodiment, an area of increased wallthickness or retaining feature 1715 can be disposed on bulb portion 1714opposite to tail portion 1717. The retaining feature 1715 can be aportion of the pressure attenuation device 17 that is used to retain thepressure attenuation device 17 into the window of a delivery system. Theretaining feature 1715 can be an area of the balloon 1711 that is thesame or higher wall thickness than adjacent areas of the balloon 1711,or a member that is more rigid than the balloon 1711, which can beintegral to or adhered to the balloon 1711, as an example. In thecertain embodiments, balloon 1711 can be made of a sufficientlytransparent material to permit the contents housed by the balloon 1711to be seen.

The balloon 1711 can be seamless and can be substantially arcuate, withthe only exception being tail portion 1717, which is inverted and towhich the valve 1713 can be welded or otherwise attached. To minimizethe potential for encrustation, to maximize patient tolerability, or forother reasons, it is preferable that over 95% of the external surfacearea of balloon 1711 be continuously arcuate and that less than 5% ofthe surface area of the balloon the balloon 1711 not be arcuate. Morepreferably, over 97% of the external surface area of the balloon 1711 iscontinuously arcuate and less than 3% of the external surface area isnot arcuate. Even more preferably, over 99% of the external surface areaof the balloon1711 is continuously arcuate and less than 1% of thesurface area is not arcuate.

For example, some embodiments of the balloon 1711 can have an overallsurface area of 4,586 mm². The external surface area of the continuouslyarcuate portion of the balloon 1711 can be 4,575 mm². The ratio ofcontinuously arcuate surface area to non-arcuate surface area for thisembodiment is 401:1. This ratio is preferably from 100:1 to 1500:1 andmore preferably from 400:1 to 600:1. The diameter of the tail portion1717 can be 0.15 inch, and the diameter of bulb portion 1714 is 1.58inches. The ratio of the diameter of the bulb portion 1714 to thediameter of tail portion 1717 is 10.53:1. This ratio is preferablybetween 6:1 and 20:1 and more preferably greater than 8:1. Withoutlimitation to any particularly theory or embodiment, it is believed thatsuch a ratio can serve to keep tail portion 1717 inverted within bulbportion 1714.

The valve 1713, which is also shown in FIG. 7, can be formed from a pairof matching, appropriately shaped, flat sheets of elastomeric material.In certain embodiments, valve can be formed in a different manner orfrom a different component. In illustrated embodiment, the pair ofmatching flat sheets can be heat-sealed to one another along theirrespective sides to form a pair of seams 1720-1 and 1720-2 and can alsobe molded so as to define a proximal section 1721, an intermediatesection 1723, and a distal section 1725. Proximal section 1721 can begenerally flat or generally frusto-conical in shape and can includeouter surfaces 1721-1 and 1721-2 that can be fixedly mounted withinopening 1719 of the balloon 1711 (FIG. 6) by a flat weld (where proximalsection 1721 is flat) or by a circumferential weld (where proximalsection 1721 is frusto-conical.) The proximal section 1721 can includean end surface 1722, which can be a surface or mating surface, intendedto interface the distal end 1527 of push-off member, thereby allowingpush-off member to push the device 17 off a distal end of an inflationtube. In some embodiments, this surface 1722 is a 90 degree flatsurface. Other surfaces, such as a concave or convex surface may alsointeract with the distal end of push-off member. The shape of the distalend of the pushoff member can be flat, concave, convex, or a shape thatpermits interaction with the end surface 1722. Intermediate section 1723can be generally cylindrical and can be reduced in inner diameter and inouter diameter as compared to proximal section 1721. Moreover,intermediate section 1723 can be reduced in inner diameter as comparedto the outer diameter of an inflation tube and can include an inner sidesurface 1724 that can be used to make a stretch interference fit withthe inflation tube so as to seal against the inflation tube or to propopen valve 1713, which will close upon release, thereby enabling theballoon 1711 to be inflated under high pressure with minimal leaking.For example, where the outer diameter of the inflation tube can be inthe range of about 0.001-5.00 inch, preferably about 0.005-0.50 inch,more preferably about 0.010-0.125 inch, the inner diameter ofintermediate section 1723 can be correspondingly smaller, for example,in the range of about 0.0005-4.900 inch, preferably about 0.001-0.49inch, more preferably about 0.005-0.120 inch. Moreover, the wallthickness of intermediate section 1723 can be in the range of about0.0001-2.00 inch, preferably about 0.001-0.24 inch, more preferablyabout 0.005-0.050 inch. In certain applications, the nominal pressureexerted on the self-sealing valve 1725 is relatively low, e.g., below 3psi. Therefore the surface area of the contact area of the two surfacesmust be sufficient to resist flow during use. This is can beaccomplished with a structure 1725 that has a width typically less than1 inch, more preferably less than 0.5 inches, and more preferably lessthan 0.25 inches. To maintain valve function, the length of thestructure 1725 can be greater than the width of structure 1725, morepreferably the length is greater than 1.5 times the width of thestructure 1725, and more preferably greater than two times the width ofthe structure 1725. Distal section 1725 can be a generally elongated,flattened structure that is self-sealing (i.e., biased, independently ofits environment, towards a closed state) and that has a distal end 1727through which fluid inputted to valve 1713, in the manner discussedherein, can exit valve 1713 to occupy the space defined by the balloon1711. Preferably, distal section 1725 is made sufficiently long tominimize the escape of fluid from within the balloon 1711 through valve1713.

Referring now to FIG. 8, there is shown a flowchart, schematicallydepicting one possible method 1731 for making the device 17. Method 1731can begin with a step 1731-1 of providing a tubular member, which canbe, for example, an extruded tube 1733 of elastomeric material having apair of open ends 1734-1 and 1734-2 (see FIG. 9A). Method 1731 cancontinue with a step 1731-2 of closing off end 1734-2 to form a tube1735 having a closed end 1735-1 (see FIG. 9B). Method 1731 can thencontinue with a step 1731-3 of blowing up or expanding tube 1735 to forma generally spherical portion 1736 and a generally cylindrical tailportion 1737 (see FIG. 9C). (Step 1731-3 can further include pulling onthe closed end 1735-1 during said expansion of tube 1735.) Method 1731can then continue with a step 1731-4 of inserting valve 1713 into tailportion 1737 and joining, such as by either a circumferential weld or aflat weld, proximal section 1721 to tail portion 1737. Method 1731 canthen conclude with a step 1731-5 of inverting the combination of valve1713 and tail portion 1737 into generally spherical portion 1736,thereby forming the device 17. In some embodiments, to prevent the valve1713 and tail portion 1737 from reversing this inverting step 1731-5during use, the valve and tail portion can be anchored to the balloonwall in any method known in the art including but not limited to use ofan adhesive or welding the distal end of the valve to the balloon wall,for example. An embodiment is to fabricate the balloon to provideincreased resistance to the reversal of inverting step 1731-5 with oneor more of the following features: 1) an increase in wall thickness orstiffness on the balloon near the area of the balloon where the tailprotrudes (for example, a circumferential increase in balloon thickness1736-1 that measures more than two times the diameter of the tail, andmore preferably more than 1.5 times the diameter of the tail, and morepreferably more than 1 time the diameter of the tail, and thiscircumferential wall thickness is less than 0.075 inches, and morepreferably less than 0.050 inches, and more preferably less than 0.025inches; 2) a wall thickness of the tail 1737 that is at least 1 time thewall thickness of the balloon 1736, more preferably at least 1.5 timesthe wall thickness of the balloon 1736, more preferably at least twotimes the wall thickness of the balloon 1736, more preferably at leastthree times the wall thickness of the balloon 1763; 3) a balloon with ameasured angle between the wall of the balloon near the tail opening andthe tail 1736-2 of at least 45 degrees, more preferable greater than 70degrees, more preferable greater than 80 degrees, and more preferableapproaching 90 degrees; and 4) a measured radius where the tail 1737interfaces with balloon 1736 of less than 0.5 inches, more preferablyless than 0.1 inches, more preferably less than 0.075 inches, morepreferably less than 0.035, and preferably 0.015 inches. Preferably,device 17 is dimensioned so that spherical portion 1736, when expanded,has a diameter that is approximately 6-20 times the diameter of theentry port defined by the interface of spherical portion 1736 andinverted tail portion 1737. In some embodiments, the shape, thicknessand material of closed end 1735-1 forms the integral retaining member1715 in the wall of the balloon. In some embodiments, the valve is notinverted and only the tail is inverted such that the tail is invertedand both the tail and valve are moved into the spherical portion.

The balloon 1711 can alternatively be made using a dip process. Forexample, Brash et al., “Development of block copolyether-urethaneintra-aortic balloons and other medical devices,” Journal of BiomedicalResearch, 7(4):313-34 (1973), which is incorporated herein by reference,describe a manufacturing process that can be used to manufacture theballoon 1711. A mandrel is formed from expendable wax, and then dippedusing commonly known balloon dipping methods to form a balloon. Uponcure of the balloon material, the wax is melted and removed, resultingin the desired balloon.

One advantageous feature of device 17 is that it can be devoid of seamson its exterior surface. The absence of such seams can be desirablesince such seams can rub up against and cause irritation with thebladder or other anatomical structure in which device 17 is positioned.In addition, such seams can become encrusted, over time, with biologicalsediment from the anatomical structure in which device 17 is positioned,which encrustation can exacerbate irritation or can otherwise beregarded as unhygienic or undesirable.

Embodiments of balloon have been described as having certain propertiesand characteristics as described in relation to specific testprocedures. In some embodiments, the balloon can be substantiallyhomogeneous such that the entirety of the balloon exhibits theproperties. For example the balloon wall thickness can be substantiallyhomogenous over the surface of the balloon. In some embodiments, theballoon wall thickness varies throughout balloon. In some embodiments, aportion of the inflatable the balloon that is less than the entirety ofthe balloon can exhibit the properties. For example a portion of theinflatable the balloon wall could exhibit the characteristics described.

As discussed herein, in some embodiments, the balloon/can have asubstantially uniform wall thickness. In some embodiments, the averagewall thickness of the outer wall of the balloon is between 0.0003 and0.005 inches, or between 0.0008 and 0.0025 inches and in certainembodiments between 0.002 and 0.0035 inches, and certain embodimentsbetween 0.001 and 0.00175 inches. In some embodiments, the minimum wallthickness of the balloon is between 0.0008 and 0.00325 inches, and incertain embodiments between 0.002 and 0.0035 inches, and certainembodiments between 0.001 and 0.00175 inches. In some embodiments, thethinnest location of the balloon also referred to as the location ofminimum wall thickness is at an equator of the balloon. In someembodiments, the balloon wall thickness varies based on materials andmanufacturing processes. In some embodiments, the balloon wall thicknessis not homogenous and can be varied. In some embodiments, the wallthickness can be varied dependent upon geometric configurations of theballoon. In some geometric configurations the balloon can be configuredso that different portions of the balloon have different thicknesses andexhibit different properties based on how the balloon is configured tobe placed within the patient. In some embodiments, the minimum wallthickness also referred to herein as the thinnest thickness of theinflatable balloon 1711 is measured from the thinnest portion of theballoon, which in some examples is at the equator of the balloon. Insome embodiments, the equator of a balloon is the widest diameter of theballoon along an axis that is perpendicular to the longitudinal axis ofthe balloon. In some embodiments, the equator of a balloon is the widestdiameter along an axis that is perpendicular to the transverse axis ofthe balloon . One can measure the thickness of the balloon by measuringthe outer wall. One can measure the thickness of the balloon by pinchinga deflated balloon and measuring two walls (double wall thickness) ofthe balloon together and dividing the value by two. In some embodiments,the average thickness of the inflatable balloon 1711 is an average ofthickness from various regions of the inflatable the balloon, such as atthe equator, regions near the poles, and etc. In some embodiments, thedouble wall thickness is used as a measurement for thickness of theinflatable the balloon. In some embodiments, the wall thickness at theequator of the balloon is the thinnest portion having the minimum wallthickness and can determine the stress and strain of the inflatable theballoon 1711.

Referring to FIGS. 10A and 10B, additional embodiments of a pressureattenuation device 66 are illustrated in which the device 66 constructedin a different manner. In the illustrated embodiment of FIGS. 10A and10B, the inflatable balloon 68 is illustrated as having a generallycircular profile, although other profiles can be used.

The balloon 68 illustrated in FIGS. 10A and 10B comprises an outer wall70, for separating the contents of the device 66 from the externalenvironment. Outer wall 70 can comprise a first component 74 and secondcomponent 76 bonded together such as by a seam 78. In the illustratedembodiment, the first component 74 and second component 76 areessentially identical, such that the seam 78 is formed on the outerperiphery of the balloon 68. Seam 78 can be accomplished in any of avariety of manners known in the medical device bonding arts, such asheat bonding, adhesive bonding, solvent bonding, RF or laser welding, orothers known in the art.

The outer wall 70, formed by a bonded first component 74 and secondcomponent 76, defines an interior cavity or interior chamber 72. As isdiscussed elsewhere herein, interior chamber 72 preferably comprises amedia that can include a compressible component, such as gas, or foam.Other media or structures capable of reduction in volume through amechanism other than strict compression can also be used. For example, amaterial capable of undergoing a phase change from a first, highervolume phase to a second, lower volume phase under the temperature andpressure ranges experienced in the bladder can also be used. In someembodiments, the media comprises a liquid that forms a solid or foamafter implantation. In some embodiments, the media comprises a solid.

To facilitate filling the interior chamber 72 following placement of thedevice 66 within the bladder, the balloon 68 is preferably provided witha valve 80. In the illustrated embodiment, the valve 80 is positionedacross the seam 78, and can be held in place by the same bondingtechniques used to form the seam 78. The valve 80 can be omitted in anembodiment in which the attenuation device 66 is self-expandable.

The valve 80 generally comprises an aperture 82, for receiving a fillingtube therethrough. The aperture 82 is in fluid communication with theinterior chamber 72 by way of a flow path 83. At least one closuremember 84 is provided for permitting one way flow through flow path 83.In this manner, a delivery system and filling device can be used todisplace closure member 84 and introduce compressible media into theinterior chamber 72. Upon removal of the filling device, the closuremember 84 prevents or inhibits the escape of compressible media from theinterior chamber 72 through the flow path 83.

Thus, the closure member 84 is preferably movable between a firstorientation in which it obstructs effluent flow through the flow path 83and a second position in which it permits influent flow through the flowpath 83. Preferably, the closure member 84 is biased in the firstdirection. Thus, forward flow can be accomplished by either mechanicallymoving the closure member 84 into the second position such as using afilling tube, or by moving the closure member 84 into the secondposition by exerting a sufficient pressure on the compressible media inflow path 83 to overcome the closure bias. Any of a wide variety ofvalve designs, including those discussed elsewhere herein, can be usedin the device 66 or device 17 described above.

In order to minimize trauma during delivery of embodiments of the device17, 66 described herein, the device 17, 66 is advantageously expandablefrom a first, reduced cross-sectional configuration to a second,enlarged cross-sectional configuration. The device 17, 66 can thus betransurethrally deployed into the bladder in its first configuration,and enlarged to its second configuration once positioned within thebladder to accomplish a pressure attenuation function. Preferably, acrossing profile, or a greatest cross-sectional configuration, of theattenuation device 17, 66 when in the first configuration is no greaterthan about 30 French in certain embodiments, 24 French (8 mm) in certainembodiments, and, no greater than about 30 French in certainembodiments, no greater than about 24 French in certain embodiments, nogreater than about 18 French (6 mm) in certain embodiments, and incertain embodiments no greater than about 14 French. This can beaccomplished, for example, by rolling a deflated balloon about alongitudinal axis, while the interior chamber is evacuated. Oncepositioned within the bladder, the interior chamber 72 can be filledwith an inflation media, such as a high vapor pressure media or such asa high vapor pressure media in combination with other gases, to producea pressure attenuation device 17, 66.

Various coatings can be used to enhance the biocompatibility of theimplantable devices 17, 66 and associated insertion or removal devicesdescribed herein. Lubricating coatings, substances, and substrates canbe used to facilitate insertion or removal. In some embodiments, thedevice incorporates biocompatible coatings or fillers to minimizeirritation to the bladder wall and mucosa and/or to inhibit theformation of mineral deposits (encrustation) or biofilm formation. Suchdevice treatments can also inhibit films, deposits or growths within oron the surface of the device. Materials can be coated onto the surfaceor incorporated within the wall of the device. Biocompatible lubricatingsubstances can be used to facilitate the placement of the attenuationdevice/fill tube within a lumen of an introducer.

As shown in FIGS. 13A-C, the human urinary bladder 5 is a solid,muscular, and distensible organ that sits on the pelvic floor. Itcollects urine excreted by the kidneys prior to disposal by urination.Urine enters the bladder 5 via the ureters (not shown) and exits via theurethra 7.

The walls of the bladder 5 are mostly comprised of muscle tissue. Thismuscle tissue is known as the detrusor muscle, and is a layer of theurinary bladder wall made of smooth muscle fibers arranged in spiral,longitudinal, and circular bundles. When the bladder 5 is stretched,nerves are activated which signals to the parasympathetic nervous systemto contract the detrusor muscle. This encourages the bladder 5 to expelurine through the urethra 7. For the urine 104 to exit the bladder, boththe internal sphincter and the external sphincter need to open. Theurinary bladder 5 can contain a wide range of urine volumes, from 0 toas much as about 600 ml of urine. Typically, in a female, bladder urinevolumes range from 0 to about 300 ml. Typically, in a female, a fullbladder will contain about 250 to 300 ml.

The neck of the bladder is the area immediately surrounding the urethralopening; it is the lowest and most fixed part of the organ. In the maleit is firmly attached to the base of the prostate, a gland thatencircles the urethra. The bladder neck is commonly more or lessfunnel-like in shape. The angle of inclination of the sides of thisfunnel varies based on the degree to which the bladder is full, and alsovaries during filling and emptying of the bladder. A very full distendedbladder will have a bladder neck with more oblique walls, and a bladderthat is emptying or empty will be more acute. The posterior portion ofthe bladder neck that is contiguous with the base of the bladder has aregion containing a high density of sensory nerves. This region istriangular in shape and is known as the trigone region. This invertedtriangle defined by the urethra (the vertex of the triangle) and theureteral orifices at each corner of the base of the triangle. Theureteral orifices are the locations where the ureters enter the bladder.

The highest concentration of sensory nerve receptors in the bladder canbe found in the trigone region. Anything that causes pressure, friction,or irritation on this region can cause a number of morbidities,including urgency, frequency, pain and/or irritation. The bladder neckcontains stretch receptors, and anything that lodges in or otherwisestretches the bladder neck will likewise be very uncomfortable. Whendesigning a device that is to reside in whole or in part in the bladder,the comfort of that device will be significantly impacted by thedevice's ability to minimize or avoid contact with these twoparticularly sensitive areas.

In addition, the bladder does not contract or expand uniformly. Forexample, when the bladder is full it is quasi-spheroid or ovoid inshape. Its muscular walls are stretched out. During micturition, as thebladder empties, the superior and inferolateral walls contract.Wrinkles, or rugae, form in these walls as they shrink. The bladder neckand trigone area is more firmly anchored to underlying tissue and doesnot shrink as significantly or form rugae. Consequently the shrinkage ofthe bladder is not uniform and most of the reduction in size comes fromthe shrinkage of the superiolateral and inferolateral walls, and fromthe superior wall, or dome, becoming convex as it collapses towards thetrigone and bladder neck area.

Accordingly, intravesical implants can preferably be configured toavoid, or not be capable of entering the bladder neck and trigone area.This can reduce or eliminate irritation to these sensitive areascontaining the majority of the pain receptors in the bladder. Also,recognizing the non-uniform contraction of the bladder as it empties,other embodiments can include devices that reside in the foldedperimeter of the bladder and/or comprise an open center (such as atoroid) or perforated center (i.e., a central region that permits flowthrough) that does not contact the sensitive trigone area, andoptionally can remain in a relatively fixed location.

If the implant gets too large, then it can diminish the urine storagecapacity of the bladder to the point where the patient may need tourinate more frequently. Accordingly, one or more embodiments of devicesare adapted to not occupy more than 10% of a typical functional capacityof the bladder. In other embodiments, the volume of the implant can beas high as 20%- 50% of functional capacity. In other embodiments, thevolume of the implant can be as high as 50%-over 100% of functionalcapacity.

In certain embodiments, the pressure attenuation devices provided hereincan be suitable for providing a platform for an intravesical devicecomprising a drug delivery device, data collection device, attenuationdevice, nerve stimulation device, wave producing device, vibrationproducing device, pressure sensing device, chemical sensing device,volume sensing device, pH sensing device, or a therapeutic device. Suchfunctions may be in addition to or as an alternative to the pressureattenuation functions described herein.

As discussed previously, the pressure attenuation device 17, 66 can beat least partially expandable. Expansion facilitates delivery byallowing the device 17, 66 to assume a first delivery profile forpassage through the urethra or surgical opening in the bladder and toassume a second expanded profile operable to prevent the implant fromentering the trigone region. In some embodiments, the expanded device17, 66 can be characterized by one or more dimensions greater than thesmallest cross-section distance of the trigone region. FIG. 13Bschematically illustrates an embodiment of a pressure attenuation device17, 66, which can be configured according to the embodiments describedherein, positioned within the bladder 5.

Attenuation

FIGS. 11A-11D illustrate the principle of attenuation (i.e., pressurereduction) with various attenuation device air volumes. The data forthese graphs were generated using a bench top bladder simulationprogram. Here, the maximum spike pressure is 2.0 psi. The spike eventduration is approximately 40 ms, which is approximately equivalent tothe duration of a coughing or sneezing event. With reference to FIG.11A, a test was conducted with a 250 ml rigid plastic container filledwith synthetic urine or water. A regulated pressure of 2.0 psi wasintroduced into the container via a controlled solenoid valve. Apressure transducer detected the pressure rise. Here, the pressure risetime (Tr) of the container pressure 422 to reach 2.0 psi wasapproximately 40 msec. With reference to FIG. 11B, a similar test wasconducted on a 250 ml rigid plastic container. Here, an attenuationdevice filled with 15 ml of air was placed inside the container filledwith synthetic urine. Here, the Tr of the container pressure 424 toreach 2.0 psi was approximately 195 msec. Thus, the attenuation deviceslowed the rise time by 4.8×. During the spike event (i.e., when timeequaled 40 msec), the pressure inside the container reached 0.7 psi (vs.2 psi), resulting in a 65% reduction of pressure vs. baseline. Withreference to FIG. 11C, a similar test was conducted; the only differencebeing that the attenuation device was filled with 25 ml of air. Here,the Tr of the container pressure 426 to reach 2.0 psi was approximately290 msec. Thus, the attenuation device slowed the rise time by 7.25×.During the spike event (i.e., when time equaled 40 msec), the pressureinside the container reached 0.5 psi (vs. 2 psi), resulting in a 75%reduction of pressure vs. baseline. With reference to FIG. 11D, asimilar test was conducted; the only difference being that theattenuation device was filled with 30 ml of air. Here, the Tr of thecontainer pressure 428 to reach 2.0 psi was approximately 340 msec.Thus, the attenuation device slowed the rise time by 8.5×. During thespike event (i.e., when time equaled 40 ms), the pressure inside thecontainer reached 0.4 psi (vs. 2 psi), resulting in an 80% reduction ofpressure vs. baseline.

FIGS. 12A-12D show pressure vs. time curves generated by a bench topbladder simulator. FIG. 12A shows the baseline pressure-time curvewithout an attenuation device. FIG. 12B shows the pressure-time curvewith an attenuation device having a 15 cc air volume. FIG. 12C shows thepressure-time curve with an attenuation device having a 25 cc airvolume. FIG. 12D shows the pressure-time curve with an attenuationdevice having a 30 cc air volume.

Embodiments of the pressure attenuation devices 17, 66 discussed hereincan have the ability to treat and/or prevent stress urinary incontinenceby attenuating pressure within the bladder in a manner as describedabove . For example, a method of preventing stress urinary incontinencecan include providing a pressure attenuation devices 17, 66 operable toreversibly occupy intravesical space in response to a pressure increaseevent within a bladder said response operable to impede the rate of anintravesical pressure increase event during an initial period. Theinitial period can be around 0 milliseconds to 1 second from the event.This can beneficially allow time for neurological signaling of aguarding reflex to increase the outlet resistance of an external urinarysphincter sufficient to prevent leakage of urine through said sphincterafter said initial period. The selected treatment period canbeneficially facilitate rehabilitation of a neuromuscular system of thebladder and restoration of continence.

Pressurized Implants

All liquids (and for that matter solids) will evaporate at a giventemperature until they saturate the space above the liquid with theirvapor. The pressure exerted by that saturated vapor is the vaporpressure. The vapor pressure goes up with temperature and when a liquidis heated until its vapor pressure is greater than one atmosphere, itboils while trying to maintain the space above it at its vapor pressure,now more than one atmosphere. Likewise if the vapor of a liquid isconcentrated (e.g., compressed) to be present at a partial pressure(concentration) greater than its vapor pressure, it condenses. Someliquids have very low vapor pressures (e.g., cooking oil, high molecularweight PFCs) and some have high vapor pressures (e.g., alcohol,gasoline, lower molecular weight PFCs). Within this document theabbreviation, PFC, is used for perfluorocarbon.

Partial pressure is both a measure of pressure (force/area) and a unitof gas concentration (at constant temperature, proportional tomoles/volume). A “p” placed in front of the chemical symbol of a gasgenerally denotes it as the partial pressure of that gas, e.g., pCO₂.The total of all partial pressures inside a container is the gaspressure measured inside that container. Diffusion is controlled by thedifference in concentration across a boundary or membrane and thus forgases the rate is proportional to the difference in partial pressures ofthe gas on both sides of a membrane.

Gas tension is a measure of the amount of a gas dissolved in a liquid(e.g., O₂ or CO₂ in blood, urine). It is a preferred measurement for theliquid systems described here. Gas tension is defined as the partialpressure of a gas that would equilibrate with the liquid sample causingit to contain the same quantity (g/ml or moles/liter) of that gas as isin the test sample. It is expressed as a partial pressure with units ofmm Hg, torr, or cm H₂O.

Many of embodiments of the devices described herein rely on complianceto attenuate or buffer pressure spikes, such as in the bladder.Compliance is the change in volume (V) of a device per unit change inapplied pressure (P) on the device (dV/dP). This is the slope at anypoint in a plot of volume (V) of the device vs. pressure (P) applied tothe device. For example, compliance is often calculated from V vs. Pcurves of the lung to indicate the effort needed to breathe. In our caseit is a measure of how capable a device is of dampening a pressurespike. High compliance means a large device volume reduction to relievea given pressure spike. Since the V vs. P curve is often non-linear, theslope, dV/dP=compliance, is not constant throughout the working regionof a device. Internal gas pressures, geometry of the device, volume ofthe device and elasticity of the skin of the device can be chosen tomaximize compliance under the conditions expected for each application.

Tables and charts are readily available which show the vapor pressure ofa given PFC as a function of temperature and can be useful in designinga device with certain pressure properties, as shown herein.

For liquids, the amount of dissolved gas is stated as a gas tension.This is the equilibrated partial pressure of the gas that results in theamount of dissolved gas. Since this is the liquid concentration that isrelevant for diffusion across biological membranes, it is commonly usedin medicine for gases in the blood e.g., pO₂ or pCO₂ and has units ofpressure, e.g., mm Hg, or cm H₂O. Gas tensions are actually a measure ofsaturation level rather than true concentrations. Thus, a sample ofblood with an N₂ tension of 593 mm Hg or O₂ tension of 160 mm Hg wouldbe saturated with those gases when exposed to a gas mixture containingpartial pressures of 593 mm Hg of N₂ or 160 mm Hg of O₂. This isregardless of how many moles or milligrams per ml were dissolved in thesample. Unlike gaseous systems where compression of the system elevatesthe gaseous partial pressures in the system, gas tensions of gasmolecules dissolved in an incompressible liquid are not affected byhydrostatic pressures.

Another factor to consider is the fact that a vessel/balloon containinga gas and/or a liquid could be constructed of an elastic material. Asthe pressure of gas inside the balloon increases relative to thepressure outside the vessel, the vessel can seek to expand to neutralizethe difference in pressure between inside and outside the vessel. As thevessel expands it will stretch and exert a force which countermands theforce of the gas pressure within. This is sometimes known as skintension causing skin pressure. Thus, an equilibrium state could existwhere the pressure outside such an elastic vessel is 760 mm Hg, thepressure inside the vessel is 780 mm Hg, and the skin tension of thevessel exerts a force on the gas within it that is equal and opposite tothe expansionary force of the extra 20 mm Hg within the vessel.

It is important to consider the gases and the concentrations of thosegases which can be found within the body when placing an implanttherein. Generally, there is a close relation to the gases found in theambient atmosphere outside the body, and those within. In normal air,the largest component is nitrogen. The components of a gas are, in factreferred to according to their partial pressures. That is, when it issaid that air is 78% nitrogen, it means that this is the percentage ofthe total gas pressure due to nitrogen. The second most common componentis oxygen, whose partial pressure contributes 21% of total atmosphericpressure. Other gases make up the remaining 1% (e.g., CO₂ is 0.04% andthus can be neglected in most calculations discussed herein) of thetotal pressure. Also, the body does not metabolize nitrogen, and it ispresent within the body's fluids, and its partial pressure contributionis related to its contribution outside the body, limited by itssolubility in the respective fluids. Thus, if the ambient pressure is760 mm Hg, then the total pressure is 760 mm Hg, the partial pressure ofnitrogen is 593 mm Hg or 78%. The partial pressure of oxygen, expressedas pO₂, is 160 mm Hg, or 21%. The partial pressure of the remaininggases would be about 8 mm Hg, or about 1%.

The nitrogen concentration in blood is related to nitrogen's solubilityin blood but, since it is not metabolized, its gas tension isessentially equal to the nitrogen partial pressure in air. The oxygenconcentration in blood is more complex, since oxygen is actively boundto hemoglobin in the blood—boosting blood's capability to carry oxygen.Also, unlike nitrogen, oxygen is metabolized in the body, so itsconcentration can vary significantly within the body. The amount ofoxygen present in blood varies and is reported as “oxygen saturation,”or the % of the maximum oxygen that blood can carry or the oxygentension pO₂. For a healthy person, this is typically in the range of 95to 98%. Venous blood is typically in the range of 60 to 80%. Whenconsidering the diffusion of oxygen across membranes the preferredmeasurement is the oxygen tension or pO₂. Oxygen concentration in fluidssuch as cerebrospinal fluid, vitreous humor and bladder urine alsovaries.

In the article “Noninvasive Oxygen Partial Pressure Measurement of HumanBody Fluids in Vivo Using Nuclear Magnetic Imaging” by Zaharchuk et al.(Acad. Radiol. 2006; 13:1016-1024), a table of gas tensions of oxygen invarious body fluids is detailed. Information from that article issummarized in Table 1, below. The authors, Zaharchuk et al., attemptedto measure partial pressure of gases in the body using MM. In an effortto verify their measurements they performed a literature review to seewhat other researchers had estimated the partial pressures to be.

In Table 1, the oxygen partial pressure for particular bodily fluids isgiven. The middle column is Zaharchuk's measurement and the right columnis what they found by studying the literature. Also, one should notethat the partial pressure of oxygen in the atmosphere is 160 mm Hg andthus fully air equilibrated fluids, if there were no consumption, wouldhave oxygen tensions of 160 mm Hg.

TABLE 1 Body Fluids and Oxygen Partial Pressure Values Actual pO₂measured Literature Review “best by Zaharchuk estimate” range Body Fluidet al. (mm Hg) of pO₂ (mm Hg) Cerebrospinal fluid in 52 +/− 14 30-74Lateral ventricles Cerebrospinal fluid in 62 +/− 29 31-74 Cisterna magnaCerebrospinal fluid in 138 +/− 46  Not Found in the cortical sulcalLiterature Cerebrospinal fluid in 69 +/− 22 40-57 lumbar subarachnoidVitreous Humor 63 +/− 34  9-20 Bladder Urine 63 +/− 16 25-80

Pressure within the abdomen and within the bladder is typically measuredin units of “centimeters of water” or cm H₂O, where 1.0 mm Hgcorresponds to 1.33 cm H₂O. So, for example, the partial pressure ofoxygen in atmospheric air is about 212 cm H₂O, and the partial pressureof oxygen in bladder urine is approximately 84 cm H₂O. Hence, there is apartial pressure “deficit” of oxygen in bladder urine corresponding toapproximately 128 cm H₂O.

Provided herein are improved pressurizable, compressible, and/orexpandable devices for attenuating pressure waves or spikes in the bodyand for preventing or relieving various pathological conditions andimproving surgical outcomes.

Several of the therapeutic devices herein are comprised of implantableballoons, vessels, enclosures, envelopes, pistons, or hydraulic devicesthat contain gas or gas/liquid mixtures. Such devices can define a rangeof permeability. Examples of such devices can be found in U.S. Pat. No.7,347,532 and US Publication No. 2007-0156167 herein incorporated byreference. Various embodiments herein provide for rapid, delayed, orcontrolled in situ inflation or deflation. In other embodiments, thedevices are further comprised of relatively soft, distensible, thin, andconsequently gas permeable membranes. Over time these devices willdeflate and become ineffective or fail unless fitted with a “gasgenerator” of a selected high vapor pressure media. Certain othermethods and devices provided herein include the maintenance of inflationfor a selected period of time by providing the pressure attenuationdevice with a high vapor pressure media.

In some embodiments, the pressure attenuation device 17, 66 as describedherein is placed in the bladder to attenuate pressure spikes that wouldotherwise cause urinary incontinence. As shown in FIGS. 13A and 13B,pressure “P” on the bladder, for example from physical activity cancause urine leakage 104 in those who suffer from urinary incontinence.Embodiments of the implant 17, 66 (schematically illustrated in FIG. 13Bas positioned within the bladder) can be positioned within the bladderto absorb the pressure in the bladder so that there is no urine leakage.

The pressure within the bladder is typically a little bit higher thanatmospheric pressure, since it typically contains urine which displacesthe bladder's muscular walls. The walls of the bladder, through theirmuscle tone and mass, exert force on the urine inside, resulting intypical pressures that can be around 15 cm H₂O above atmospheric in somepatients. For the sake of simplifying discussion in this document, wewill simply use this number as an approximation of average bladderpressure. If the balloon is under-filled with air such that there is noskin pressure to consider, then there will be a situation immediatelybefore the balloon is placed in the bladder where the pressure withinthe bladder is atmospheric plus 15 cm H₂O, and the pressure within theballoon is atmospheric pressure. When the balloon is placed within thebladder, the balloon will instantaneously compress, so that its contentsare at the same total pressure as the hydraulic pressure with which theurine in the bladder is pressing on the balloon. That is, the nowslightly compressed gas will press outwards on the walls of the balloonwith the same force that the liquid in the bladder will push inwards.This “force equilibrium” of exactly equal and opposite forces exertedfrom within the balloon outwards, and outside the balloon inwards is oneequilibrium that should be considered in this example.

In the force equilibrium, the liquid or hydraulic pressure within thebladder pushes on the balloon, and the now slightly compressed gaswithin the balloon pushes outwards on the liquid. The inwardly pushingforces should balance with the outwardly pushing forces or the balloonwill either burst or collapse.

The second equilibrium to be considered is partial pressure equilibrium.The partial pressures of the individual gas constituents within theballoon will seek to equilibrate with the gas tensions of the dissolvedgas in the liquid outside the balloon.

In this example, first assume that initially, before the balloon wasinserted, that the proportions of gas in atmospheric air were in theballoon, and that the same proportions of dissolved gas existed in theurine. The balloon was compressed slightly when it was inserted, so allof the partial pressures of the gas constituents increased by an amountproportional to the decrease in volume due to the compression. Thisresults in a situation where there will be higher partial pressures ofthe individual gas components inside the balloon versus the gas tensionsof the same gases outside the balloon. This will result in diffusion ofthese gases out of the balloon into the urine. As the gases leave theballoon, the balloon will shrink to maintain the force balance. In thisexample, this net out-of-the-balloon gas diffusion will continue untilthe balloon is completely empty. The rate of deflation will be afunction of the permeability of the membrane to the gases held withinand the difference between the hydrostatic pressure in the bladder andthe total gas tension of gases dissolved in the urine.

In one aspect of certain embodiments of the disclosure is the additionof a high vapor pressure media such as PFC to the contents of theballoon. Since some selected or preferred PFCs have high vaporpressures, the partial pressure of the PFC will add to the existingpartial pressures of the other gases to increase the overall gaspressure in the device. A small amount of liquid high vapor media suchas PFC within the balloon serves as a reservoir or generator and willoffset losses due to slow diffusion and maintain a constant PFC partialpressure.

The stable size of the balloon depends on the maintenance of a supply ofliquid high vapor pressure media such as PFC inside the balloon, thebalance of force as regulated by balloon size, and the balance ofpartial pressures. If any of these key factors moves out of balance theballoon will either grow or shrink.

Selection and Determination of the Vapor Pressure or Partial PressurePFC Element

In a simplified embodiment involving an air-filled balloon placed intothe bladder or other liquid filled bodily organ one will note that thedevice will float in the bladder and rest near the top of the bladder.It will not deflate; therefore there is equilibrium between the airinside the balloon and the liquid pressing upon it. The gas moleculesinside the balloon provide an internal force (F_(int)) that pressesoutwards, and the hydraulic pressure of the urine provides an externalforce (F_(ext)) that presses inward on the balloon. For the balloon toexist, the forces should be in balance as illustrated here, that isF_(int)=F_(ext). The internal force is created by the pressure of thegas inside the balloon.

In this example, the gas inside the balloon was normal atmospheric air,at sea level, when it was inserted. So its total pressure beforeinsertion was approximately 760 mm Hg which is approximately equal to1000 cm H₂O. This total pressure of 1000 cm H₂O is, as described byDalton's law, equal to the sum of the partial pressures of its gascomponents. Normal atmospheric air is comprised of approximately 78%nitrogen, 21% oxygen, and 1% other gases. Since the total pressure is1000 cm H2O, we can surmise that the partial pressure of nitrogen orP_(N2) is equal to 780 cm H₂O, the partial pressure of oxygen or Poe isroughly 210 cm H₂O, and the partial pressure of other gases or P_(OG) is10 cm H₂O. The partial pressures and total pressure of the balloonoutside the bladder are shown in Table 2.

TABLE 2 Internal Balloon Pressure When Outside the Bladder P_(N2)= 780cm H₂O P_(O2)= 210 cm H₂O +P_(OG)= 10 cm H₂O Balloon total pressure=1000 cm H₂O

As soon as the balloon is inserted into a urine filled bladder or organ,it will be subjected to hydraulic pressure due to the muscle tone of theabdomen and bladder pressing on the urine within. This is a frequentlymeasured physiological parameter, and 15 cm H₂O is a typical value, sowe will use this in our example. Now, the patient into whom the balloonhas been inserted is residing at sea level, so this “inside the bladder”(or intravesical) pressure is equal to the sum of atmospheric pressureplus the 15 cm H₂O, or 1015 cm H₂O. This means that in order to satisfythe force equilibrium, the total pressure inside the balloon changes sothat it equals 1015 cm H₂O also. It does this by compressing and gettingsmaller. The balloon will instantaneously compress as it is insertedinto the bladder. According to Boyle's law, the pressure and volume of agas are directly proportional according to the relationship: P₁V₁=P₂V₂.This means that in order for the gases' volume to decrease, its pressureincreases, in this case by 15 cm H₂O or by 1.5%.

The total pressure of the gas inside the balloon has now changed, due tothe compression, but the molar quantities and proportions of the gaseswithin has not changed. Table 3 shows the partial pressures and totalpressure of the balloon inside the bladder are (with rounding).

TABLE 3 Internal Balloon Pressure When Inside the Bladder P_(N2) = 780 +1.5% = 792 cm H₂O P_(O2) = 210 + 1.5% = 213 cm H₂O +P_(OG) = 10 + 1.5% =10 cm H₂O Balloon total pressure= 1015 cm H₂O

In this example, gas diffusion equilibrium should also be considered.Urine in the body, like other body fluids, contains dissolved gas. Theamount of gas dissolved in these fluids is governed by the gases'solubility in the fluid, and whether or not it reacts chemically orbiologically with the fluid. For example, blood can contain a muchhigher percentage of oxygen than water, due to the fact that the oxygenis bound to the hemoglobin in red blood cells. The gas tensions of gasesin urine will be different than the partial pressures of gases found inatmospheric air (most likely lower). The gas tensions will also not begoverned by the hydraulic pressure of the fluid, since these fluids are,relative to gas, incompressible and hydraulic pressure does not affecttheir solubility.

In an embodiment wherein the balloon is constructed of a material thatis permeable to gas, the gas will seek to diffuse from the high partialpressures in the balloon into the liquid where the gas tensions arelower. For example, consider the fact that the partial pressure ofoxygen in bladder urine could be around 84 cm H₂O (as describedpreviously) and in this example, the partial pressure of oxygen is 213cm H₂O in the balloon. This gradient will result in oxygen exiting theballoon at a rate determined by the gas permeability of the wall of theballoon. As the oxygen exits, the balloon will shrink to maintain theforce equilibrium. This exiting of oxygen, and balloon shrinkage will beechoed by nitrogen and the other gases present, although at varyingrates. The end result will be complete deflation of the balloon overtime.

A means to maintain balloon inflation, as described herein, is toprovide a supply of liquid PFC inside the balloon. The liquid PFC willrapidly vaporize, and provide a supply of PFC gas whose partial pressureis “locked” at the vapor pressure of the PFC. This PFC will not diffuseout of the balloon as it is not soluble in water or urine. Let'sconsider a balloon containing a PFC whose partial pressure is 120 cmH₂O, plus normal air, inserted into the bladder as before. Table 4 showsthe partial pressures, if the balloon was hypothetically filled outsidethe bladder at atmospheric pressure, before the PFC has a chance tovaporize.

TABLE 4 Internal Balloon Pressure Before Vaporization P_(N2)= 780 cm H₂OP_(O2)= 210 cm H₂O P_(OG)= 10 cm H₂O +P_(PFC)= 0 cm H₂O Balloon totalpressure= 1000 cm H₂O

In an example embodiment, outside the bladder situation, as the PFCvaporizes, the balloon will expand to maintain the force equilibrium.The gas quantities and proportions other than the PFC will remainconstant, so they are, in effect, diluted by the PFC whose partialpressure will be fixed at its vapor pressure of 12-cm H₂O. Thus, momentslater, the partial pressures in the now expanded balloon will be asshown in Table 5. The balloon will have expanded 12%, the partialpressures of the constituent gases other than PFC will maintain theirproportions since the moles of gas are the same; however they willreduce proportionally as shown:

TABLE 5 Internal Balloon Pressure After Vaporization P_(N2)= 686 cm H₂OP_(O2)= 185 cm H₂O P_(OG)= 9 cm H₂O +P_(PFC)= 120 cm H₂O Balloon totalpressure= 1000 cm H₂O

If this balloon is placed into the bladder, then the bladder pressure,15 cm H₂O, should equilibrate to a new total pressure of 1015 cm H₂O asbefore. The balloon will shrink by 1.5% and the new partial pressuresare shown approximately in Table 6.

TABLE 6 Internal Balloon Pressure After Vaporization When Inside theBladder P_(N2)= 697 cm H₂O P_(O2)= 189 cm H₂O P_(OG)= 9 cm H₂O +P_(PFC)=120 cm H₂O Balloon total pressure= 1015 cm H₂O

If the gas tension of dissolved gas in the urine is lower than the newpartial pressures in the balloon, gas will be driven out of the balloonat a rate which is regulated by the gas permeability of the balloon, andthe balloon will shrink. If the partial pressure of the dissolved gas inthe urine is higher than these new partial pressures, then gas will bedrawn into the balloon at a rate which is regulated by the gaspermeability of the balloon, and the balloon will grow. However, thepartial pressure of the PFC will remain fixed. Note that for simplicity,this example excluded the impact of the skin tension of the balloon. Thenext example will consider skin tension.

The partial pressure of the PFC can be selected by tuning its vaporpressure. In order to maintain a balloon whose volume is stable, the PFCshould be selected so that a diffusion balance is maintained. Theformula can be derived as follows. First, the pressure inside theballoon equals the pressure outside the balloon, or else the balloonwill collapse or burst.

P _(Inside Balloon) =P _(Bladder-avg) +P _(Skin-tension)   (1)

As discussed herein, P_(Inside Balloon) (the pressure inside theballoon) is equal to the sum of the partial pressures of the gaseswithin the balloon. As shown here, it is also equal to the hydraulicpressure pushing upon it plus the pressure due to the balloon skin. Theterm, P_(Bladder-avg), comprises the hydraulic pressure pushing upon theballoon due to abdominal pressure, bladder muscle tension and otherfactors. The skin pressure, P_(Skin-tension), is the inward forceexerted by the stretching material of a balloon's walls, or in othercases, simply the weight exerted on the gas within by a flaccid underinflated balloon. This equation is simply another version of the “forceequilibrium” equation described earlier.

At the same time, recall that the total pressure within the balloon isequal to the sum of the partial pressures of the gases it contains:

Note: All pressures below are absolute pressures

P _(Inside Balloon) =P _(N2-balloon) +P _(O2-balloon) +P_(other gases-balloon) +P _(PFC)   (2)

Since the partial pressure of the other gases is only 1% of the sum ofall the non PFC gases, this can be approximated as being zero, so:

P _(Inside Balloon) =P _(N2-balloon) +P _(O2-balloon) +P _(PFC)   (3)

Equation (1) from the force equilibrium was as follows:

P _(Inside Balloon) =P _(Bladder-avg) +P _(Skin-tension)   (1)

Therefore combining equations (1) and (3) gives:

P _(Bladder-avg) +P _(Skin-tension) =P _(N2-balloon) +P _(O2-balloon) +P_(PFC)   (4)

Over time, gas diffusion will occur, and P_(N2-balloon) andP_(O2-balloon) will equilibrate to values that approximate the partialpressures of oxygen and nitrogen dissolved in the urine (their gastensions). Therefore:

P _(N2-balloon) +P _(O2-balloon) =P _(Dissolved gas)   (6)

And by combing (4) and (6) we get:

P _(Bladder-avg) +P _(Skin-tension) =P _(Dissolved gas) +P _(PFC)   (7)

Or

P _(PFC) =P _(Bladder-avg) +P _(Skin-tension) −P _(Dissolved gas)   (8)

Where:

P_(PFC)=The desired vapor pressure of the PFC.

P_(Bladder-avg)=The average bladder pressure over time (i.e., course ofa day) or more generally, the anatomical environment/hydrostaticaverage.

P_(dissolved-gases)=The total gas tension of bladder urine.

P_(skin tension)=The inward force exerted by the skin of the balloon.

More generally, the equation for selecting a PFC suitable formaintaining a pressurized device according to one or more aspects of thedisclosure in a given anatomical environment is:

P _(PFC) =P _(anatomical environment/hydrostatic-avg) +P _(Skin-tension)−P _(Dissolved gas)   (9)

In another embodiment the selection for the high vapor pressure elementcan be described as:

atmospheric pressure+Ppfc=external pressure or loads on implant   (10)

Where the external loads include: tension generated by skin of theballoon, normal somatic pressure during fill and void of organ (ifapplicable), transient somatic pressure, e.g., abdominal, patientgenerated valsalva, bodily weight on organ e.g., abdominal weight onbladder or on bladder wall/balloon when the bladder is empty,differential between gas tensions in body fluid and partial pressureswithin balloon.

Having shown how to determine an appropriate vapor pressure for the PFCelement, one can now select an appropriate mixture of PFCs toapproximate this value. The P_(PFC) can be selected by mixing PFCs ofdifferent vapor pressures, and calculating the composite vapor pressurebased on the proportions of the moles of the individual PFCs.

One consideration is the average pressure within the desired area of thebody (P_(anatomical environment/hydrostatic-avg)). In the example of adevice implanted in the bladder, the average pressure within the area ofthe body would be a time average of the pressure in the bladder(P_(Bladder-avg)). This would encompass the average of: the low pressureof slowly filling bladder; pressure spikes from events such as laughs,coughs or sneezes; higher pressures achieved during micturition, orduring valsalva. Other hollow organs and tissue sites would similarlyvary in pressure ranges, from which an average value could becalculated.

Another consideration is the total gas tension of the bodily fluid inthe particular area of the body (P_(Dissolved gas)) to be treated. Thisincludes all the dissolved gases in the bodily fluid such as oxygen,nitrogen, carbon dioxide, or other gases. In the bladder, the bodilyfluid is urine. The total gas tension in urine can vary based on thepatient's diet, presence of substances in the urine that bind oxygen orother gases, or the gases that the patient is inhaling. For example, apatient breathing pure oxygen would have a higher oxygen gas tension. Itis also worth noting that gas tension will almost always be less thanthe hydrostatic, anatomical pressure, or bladder/organ/implantation sitepressure. Also note that the driving force for deflation is that theconcentration of gases inside the device is higher than the total gastension outside the device.

Several of these parameters will vary from patient to patient. Forexample, average bladder pressure in men is generally higher than thatof women. Average bladder pressure can vary from person to person withina gender based on how full each individual lets their bladder get beforevoiding. Also, average bladder pressure can vary due to pathology, forexample, due to a condition known as detrusor instability which causesundesired contractions of the bladder's muscular walls. Bladder pressurecan also vary due to physical activity. One would expect that theaverage bladder pressure of a weight lifter would be higher during aweight lifting competition than it is for a sedentary individual. Asmentioned herein, the bladder gas tensions can vary based on diet, lungfunction, metabolic rate, and other factors.

An additional consideration is the skin tension of the balloon. The skintension of the balloon can vary based on many factors, including thematerial of the balloon, the thickness of the material, and its means ofconstruction. It can also vary based on how “stretched” it is. Forexample, a balloon that has a volume of 3 ml when empty and is filledwith 15 ml will be much more stretched than the same balloon filled to 5ml.

It is conceivable that a balloon that has a stable volume over timecould be created by measuring each of the above parameters and selectingthe PFC based on that. Also, an individual could be “titrated” so thatvarious PFCs are tried and one that is stable over time is selected. Acombination of the two methods could be used as well—for example, grossmeasurement of physical parameters followed by “trying” PFCs ofdifferent partial pressures.

Various means could be used to achieve this measurement and/ortitration. For example, a pressure sensor that resides in the bladderand either transmits data out of the bladder telemetrically, or storesit for later retrieval, could be used to determine average bladderpressure. Pressure information of other hollow organs such as the eye,heart, cranium, lungs, stomach, liver, gall bladder, etc. or bodilysites could similarly be obtained. Sensors, such as those used for bloodgas measurement could be used to measure the total gas tension of urinein the bladder and the individual tensions of the constituent gases.Finally, balloons can be selected or filled in order to achieve adesired skin tension. Test device involving balloons with strain gaugesand pressure gauges to record or transmit data for short time could alsobe used to determine pressures and skin tension values.

Two examples of how the gas pressures in urine could be measured includethe use of a blood gas analyzer, such as those available from RadiometerAmerica Inc. or the MRI approach described by Zaharchuk et al.,referenced herein.

A blood gas analyzer can be used to sample gases in the urine. Apatient's bladder would be allowed to fill normally. A catheter or tubewould be inserted into the patient's bladder. Urine would be extractedinto a syringe or vial. The vial would be inserted into the machine, andstandard readouts can be obtained. PO₂ (partial pressure of oxygen inthe sample) is an example.

The blood gas analyzer runs the risk of inaccuracies related to howquickly the measurement is performed. The sample can become contaminatedin the time between taking the sample and sending to the lab. Also, themeasurement may not be as accurate as needed since there is measurementerror in the machine. A difference of 10 cm H₂O can be enough to makethe difference with regard to a balloon inflating or deflating thus,these inaccuracies can be make the error too great to be useful.

Concerning MRIs, MRI machines are big, and expensive. Thus, it is notpractical to place every patient inside an MRI machine. Furthermore theaccuracy of the method ranges from +/−14 mm Hg to +/−46 mm Hg. 14 mm Hgcorresponds to +/−18.6 cm H₂O, too broad a range for most applicationsdescribed herein.

A preferred method is to “titrate” the PFC. First, based on theinformation described herein the Physician can estimate the relative gaspartial pressures in urine and the needed partial pressure of the PFC.For example, the estimate can be in the range of 100 to 130 cm H₂O. Aclinical study can be performed in which a series of patients arestudied using balloons containing PFC with a partial pressure of 110 cmH₂O. The state of these patient's balloons upon removal would bemonitored carefully. One possible result is that on average the balloonscould be decreasing slightly in size over a 3 month period. Continuingthe example, another series of patients could be studied using a PFCwith a vapor pressure of 120 cm H₂O. Upon examining their balloons after3 months, one possible result is that their balloons could be growingslightly in size over 3 months. This result would tell us that the idealvapor pressure would be in between 110 and 120 cm H₂O. The next stepwould be to try a series of patients with a vapor pressure of 115, andso on.

One advantage of the titration method is that the desired outcome is thebest partial pressure on average over time. The partial pressure ofoxygen in urine, for example, will change over the course of the day. Itis likely to be different during sleeping and waking hours. It can alsobe affected by diet, for example, eating foods rich in ascorbic acid(vitamin C) can affect oxygen partial pressure. The titration methodyields the value that is optimum for the long term successful inflationof the balloon. Other methods that provide an instantaneous measurement(such as blood gas monitors or MRI) would not provide this benefit. Itwould be impractical to make such measurements many times over thecourse of a day, days, or even weeks or months.

Setting the Vapor Pressure of the Selected PFC Element

The PFC vapor pressure of the PFC element or additive can be set bychoosing the molecular weight/number of carbons and isomer form of thePFC (rings, branched, linear) or using hetero-atoms such as Br or H.These pure compounds will have a constant vapor pressure throughout thelife of the device as it very slowly looses PFC through the aqueousfluid surrounding the device.

Intermediate vapor pressures can also be produced by using mixtures ofPFCs, though these mixtures will change component ratios after initialvaporization and slowly through the life of the device. If mixtures areused, an excess quantity of PFC should be put in the device to minimizethe vapor pressure changes (unless we want the vapor pressure and thusinflation pressure to slowly decrease). The vapor pressure of a liquidmixture can be predicted by Raoult's Law where the total vapor pressureis the sum of each component PFC vapor pressure times its mole fractionin the liquid. This means the most volatile component leaves faster andthe vapor pressure of the remaining PFC mixture slowly drifts toward thevapor pressure of the least volatile component in the mixture. Thiseffect is exacerbated as the higher vapor pressure PFCs also are ingeneral lower in molecular weight so they also diffuse faster and havehigher water solubilities.

Examples of PFCs suitable for use as a high vapor pressure media invarious devices described herein include: perfluoropropane,perfluorobutane, perfluoropentane, perfluorohexane, perfluoroheptane,perfluorooctane, perfluorononane, perfluorodecane,perfluorooctylbromide, perflubron, and perfluorodecylbromide. Asexplained herein, two or more PFCs can be combined to form a liquidmixture with a particular vapor pressure according to their molefraction in the liquid. A preferred range of vapor pressures for a PFCelement in one or more embodiments is around 50-200 cm H₂O. In otherembodiments the preferred range of selected vapor pressures for a PFCelement is around 100-150 cm H₂O. In other embodiments, for example inthe bladder, the preferred range of selected vapor pressures for a PFCelement is around 115-130 cm H₂O, around 120 cm H₂O or around 115-117 cmH₂O. For example, in some embodiments a mixture of about 0.5 moleperfluorooctane and about 0.5 mole perfluoroheptane can result in avapor pressure of between around 115 and 130 cm H₂O at 37° C. In anotherexample, a mixture of 0.545 mole perfluorooctane and 0.455 moleperfluoroheptane can result in a vapor pressure of about 120 cm H₂O. Thepreferred range of selected vapor pressures for a PFC element can bebased in part on pO₂ of the anatomical structure. Thus, for example,areas of the body with a pO₂ similar to that of the bladder can also usea similar PFC pressure range. As pO₂ increases the desired PFC vaporpressure range decreases.

Volumes of the PFC element are generally limited by the volume of theorgan or tissue site in which the implant containing the PFC element isimplanted and by the duration in which the pressurization is intended tobe maintained. A preferred range of volumes for a PFC element within animplant according to one or more embodiments is around 0.1-10 ml andmore preferably around 0.2-0.6 ml in certain applications involving theeye or the bladder. Total volumes of implants such a balloons or theballoons according to one or more embodiments can vary from 0.1 ml to1.0 L.

The preferred volume for an implant will vary based on a variety offactors. The following example demonstrates some of the considerationsfor the total volume of an implant in a particular application. Apressurized implant is added to the bladder in order to attenuatepressure pulses in the bladder associated with stress urinaryincontinence leakage. The clinical efficacy (preventing leakage) isincreased by increasing the volume of the implant. In testing, it hasbeen determined that efficacy increases proportionally to size.

The functional capacity of a typical urinary bladder is commonly in therange of 200 to 300 ml. This depends on many characteristics such asgender, age, health status, etc. If the implant is too large it willimpact the bladder's ability to perform its primary function of storingurine. “Residual volume” is a parameter that is commonly measured byurologists and it describes the measured quantity of urine remaining ina patient's bladder after they have completed voiding (i.e., they thinkthey are empty). Based on the experience of urologists it has beendetermined that a balloon as large as 30 to 40 ml will not likely benoticed by patients, specifically with regard to increasing theirfrequency of urination. Thus, a preferred balloon volume for the bladderis between 20 and 30 ml.

Selection of a PFC and Enclosure Skin Tension System

As discussed herein, one equation for the desired PFC vapor pressure is:

P _(PFC) =P _(anatomical environment/hydrostatic avg) +P _(Skin-tension)−P _(Dissolved gas)   (9)

It is possible that a skin tension and PFC could be chosen so that thetwo associated parameters for these characteristics are much, muchlarger than the other two parameters (for example between 5 and 20 timesand preferably 10 times). For example in the bladder, ifP_(Bladder-average) is on the order of 15 cm H₂O above atmosphericpressure, or about 1015 cm H₂O absolute pressure; P_(dissolved-gases) ison the order of 880 cm H₂O; then a balloon could be selected so that itsskin tension pressure is 10,000 cm H₂O or greater, and a PFC could bechosen with a vapor pressure that is approximately the same amount.Then, in theory, a system could be designed that is relativelyindependent of the average anatomical environment pressure, here bladderpressure, and independent of the gas tension of dissolved gases. This isbecause, in this example, P_(PFC) and P_(skin-tension) are approximatelyequal, and much larger than the other two terms. Similarly, devices usedin other anatomical environments and applications such as ophthalmic,vascular, cardio-vascular, renal, pulmonary, intracranial, etc., couldbe designed with similarly appropriate and corresponding skin tensionand P_(PFC) values.

Implant Compliance

An objective of certain devices according to one or more aspects of thedisclosure is to supply compliance, dV/dP or a maximum change in volumewith an elevation of pressure (P_(h), hydrostatic pressure). Thepresence of an elastic skin only slightly reduces the compliance of thedevice. Since the compliance (dV/dP) of a gas obeying Boyle's law,P₁/P₂=V₂/V₁, is inversely proportional to the absolute pressure of thegas inside the device (P_(g)); as long as the added skin pressure(P_(skin)) is significantly less than one atmosphere (760 mm Hg, 1,033cm H₂O), the compliance of the gas is only slightly reduced with anelastic skin (a skin pressure of 5% of an atm, 50 cm H₂O, has 95% of thedV/dP of gas without a skin).

The other cause for a reduction in compliance is that, as the devicevolume reduces under an external pressure increase, the pressure causedby the skin goes down, relieving some of the added pressure and reducingsome of the volume change. This effect is controlled by the slope of thevolume vs. pressure curve (V/P curve) of the device, which in turn isdetermined by the skin materials and geometry. In the case of aninelastic bag, the V/P curve starts at zero pressure at zero volume andthen jumps vertically to the volume when the bag is full (a fullinelastic bag does not stretch with more gas pressure inside) for anymeasurable pressure. This bag has no compliance at pressures thatcompletely fill it, as the slope of the V/P curve is zero. On the otherhand, a skin that is very stretchy/elastic (e.g., thin silicone) has avery gradual change in skin pressure as the volume changes (can bedesigned to have a large V/P slope at the operating volume) and onlyslightly reduces the device compliance. The small magnitudes of theseeffects are seen in a toy latex balloon that changes diameter/volumenearly as much as a free gas when the barometric pressure or altitude ischanged.

The compliance reducing effects of the skin are reduced and in somecases overcome by the compliance increasing effects of the presence ofPFC vapors, e.g., their ability to condense when compressed.

The vapor pressure of the PFC can be chosen to inflate the device atequilibrium to a volume where the V/P curve of the device has a verylarge positive slope or in other cases just below where the slopedecreases, thereby limiting maximum volume.

The V/P curve of a device can be calculated from the known elasticproperties of the material (stress/strain relationship) and mechanicalprinciples (the law of Laplace, P_(skin)=2 times the skin tension overdevice radius). In many cases it can be better to measure the V/P curveof a device by inflating it with any fluid (e.g., air or air plus PFC)and then adjusting it. The device V/P curve can be adjusted, forexample, by lowering the V/P slope using a thicker or stiffer skinmaterial. Modifying the geometry of the device can also adjust thecurve, e.g., the 1/radius law discussed herein, means that a long smallradius cylinder will have a shallower, lower slope V/P curve than asphere of the same volume.

The V/P curves of the various devices described herein can be modifiedin many ways using unique geometry, so that even essentially inelasticmaterials can have an elastic V/P curve.

Providing Skin Tension Bias to Sustain Implant Volume in ChangingPressure Environment

Various embodiments of devices described herein comprise balloons, orenclosures comprising a porous vessel where internal gases and externalgases dissolved in the body fluid interchange over time. Such balloonswill tend to expand or contract as the result of an imbalance betweenthe outside “loads” and the internal forces supporting the balloon. Withcorrect PFC vapor pressure selection a small bias can be created wherethe balloon will grow until the tension in the skin, e.g., polymer skin,counteracts the bias of the PFC. The bias can be defined as the sum ofall the partial pressures inside the balloon (PFC+air) minus theexternal sum of gas tensions or load in the surrounding environment.Turning to the equilibrium equation discussed previously, the PFCelement in this embodiment should be greater than or equal to the otherfactors:

P _(PFC) ≥P _(anatomical environment/hydrostatic avg) +P _(Skin-tension)−P _(Dissolved gas)   (11)

A balloon's internal pressure verses volume can be plotted as shown inFIG. 14. In the region from about 0 to 14 ml of volume, designated as upto “A”, the “balloon” is essentially a bag of air with zero skintension. When in this “bag region” the balloon can have markedlydecreased patient tolerability. At about 14 ml the bag becomes aballoon. Increasing amounts of volume put stress on the skin of theballoon and exert pressure on the internal gases (as in the regionaround “B”). Depending upon the balloon material and construction, thisregion of the graph showing the additional volume being gained will befairly linear. This is analogous to the elastic region of a stress vs.strain curve, which will remain linear until either the elastic limit ofthe material is reached or the material fails.

As the volume increases, the balloon continues to stretch until the wallthickness decreases such that the balloon no longer exerts increasinglevels of force on the internal gases. At this point the ballooncontinues to increase in size, however, the pressure inside the balloonlevels off and eventually drops before the balloon fails. This area isdesignated with the letter “C”. In balloons that yield, either due tomolecular motion or thinning of the wall, this region of the graph canshow slower growth or even diminishing pressure with added volume. Theactual shape of the curve is material dependent. The shape shown, forexample, is consistent with the behavior of silicone. Similar graphs canbe made for other materials.

In the region before “A” and the region designated by “C” the balloon isunstable and tends to change volume as the result of gaseous interchangeacross the skin barrier. In the region designated by “C,” the ballooncan expand and becomes unstable, then shrink (e.g., when pressure goesback down). In the region designated by “A,” the balloon can beconsidered “underinflated,” a condition that can negatively affectimplant tolerability. Balloon stability is created when a positive biasexits where the sum of the internal partial pressures is greater thanthe external gas tensions by an amount less than the height of the curveat “C”, approximately 30 cm H₂O in this example. The positive bias willincrease the balloon's volume until the skin tension increases theinternal pressure to offset the bias. At this point the balloon will bestable. It would take more internal pressure than exists within theballoon to further increase in volume, and it is not able to shrink asthe positive bias forces the balloon volume higher than the bag region(before “A”).

In this way a balloon can be engineered to remain stable in volume (asopposed to completely shrinking or expanding until failure) overextended periods of time while experiencing changes in pressure. Thiscan be done by selecting a PFC with a slight bias over the anticipatedload but, counteracted by the skin tension profile of the balloon forthat pressure range.

One method of controlling the size of an air and high vapor pressuremedia filled porous balloon in situ uses the skin tension in the balloonwall to offset a purposely created difference between the external loadand the internal resistance. This would be unnecessary if it werepossible to perfectly set the PFC vapor pressure to offset the externalload. However, because the pressure in the bladder fluctuates anddifferent patients have different average bladder pressures it can beuseful for a device to have some tolerance to naturally occurringfluctuations and/or to be able to be used in different patients. Byusing the skin tension in the manner prescribed here tolerance can beadded to the naturally occurring variations in average external load onthe balloon.

It has been shown that in the initial under-filled or “bag” region “A”of the curve or in the post-yield region “C”, it is extremely difficultto control the balloon volume over time. In order to control the balloonvolume over time in these regions, the PFC vapor pressure would have tobe set precisely and the variation within and between patients wouldneed to be very small. Conversely, by using the increasing pressure withvolume nature of the “elastic” region “B” of the curve the balloon canfind its own equilibrium and become stable in volume.

For example, if the average external load across a population were 100cm H₂O and the average external load across the patient populationvaried from 90 to 110 cm H₂O then the PFC can be blended to yield avapor pressure of 120 cm H₂O. Assuming the balloon is not initiallyover-filled, the balloon would gain volume by sucking dissolved gassesfrom the surrounding liquid environment. As the balloon increased involume the pressure would go up due to the tension created in theballoon wall. This wall stress will offset the excess vapor pressure ofthe PFC blend and the balloon will stop growing and be at equilibrium.

Another advantage to designing the system to equalize on this part ofthe curve is that the balloon volume changes little with changes in theexternal load. This is because in order to offset small changes inexternal load a relatively large change in pressure is required.

The slope of the pressure vs. volume curve in this region is the resultof the elastic modulus of the material and the geometry of the balloon.The acceptable limits of this curve are bounded by comfort andirritation which can be affected by high sloped (or stiff) balloons andpoor volume control from balloons with low slopes in this region of thecurve. Slopes of between 1 and 20 cm H₂O/ml of volume have been shown toprovide bounds to these criteria. Slopes between 3 and 8 cm H₂O/ml ofvolume can be advantageous. As previously mentioned the slope can bedesigned into the balloon by the selection of material (elastic modulus)and geometry (shape and wall thickness).

Attenuation Device with Improved Performance at Various Elevations

As discussed herein, the partial pressure of oxygen in atmospheric airis about 212 cm H₂O, and the partial pressure of oxygen in bladder urineis approximately 54-120 cm H₂O. Hence, there is a partial pressure“deficit” of oxygen in bladder urine corresponding to approximately 129cm H₂O. However, one aspect of the disclosure herein is the recognitionthat depending on a number of factors, one of which may be elevation(altitude) the partial pressure of oxygen in atmospheric air can changeand alter the partial pressure deficit of oxygen in the bladder urine.Depending on the external environment, this can have little effect.However, in some external environments, the partial pressure deficit ofoxygen can have a meaningful effect on the system balance. Theembodiments of the pressure attenuation device 17, 66 and associatedballoons 1711, 68 described herein can be configured as discussed inthis section to address this system balance and provide improvedperformance and device robustness across a range of elevations(altitudes) and/or across a range of urine pO₂ values. According tocertain embodiments, the balloons described herein can advantageously beconfigured to elastically expand through large ranges of pressure and alarge number of cycles between such ranges of pressure. In this manner,an advantage of such embodiments is that if a patient travels from, forexample, sea level to a high elevation and then returns back sea level,the balloon advantageously remains elastic and does not plasticallydeform when the patient returns to sea level.

The oxygen concentration in bodily fluids, unlike the concentration ofnitrogen, is relatively complex, since oxygen is actively metabolized inthe body. An aspect of this disclosure is the recognition that theconcentration of oxygen can vary significantly within the body. Theamount of oxygen present in blood varies and is reported as “oxygensaturation,” or the % of the maximum oxygen that blood can carry or theoxygen tension pO₂. For a healthy person, this is typically in the rangeof 95 to 98%. Venous blood is typically in the range of 60 to 80%. Whenconsidering the diffusion of oxygen across membranes the preferredmeasurement is the oxygen tension or pO₂. Oxygen concentration in fluidssuch as cerebrospinal fluid, vitreous humor and bladder urine alsovaries. The partial pressure of oxygen in the urine is generally about54-120 cm H₂O.

Turning, once again, to equation 8, shown below, the forces that canimpact balloon volume include, but are not necessarily limited toballoon skin tension (which, as discussed herein, depends on or is afunction of balloon volume), average detrusor pressure, and the partialpressure of dissolved gases in the bladder.

P _(PFC) =P _(Bladder-avg) +P _(Skin-tension) −P _(Dissolved gas)   (8)

Where:

P_(PFC)=The vapor pressure of the PFC.

P_(Bladder-avg)=The average bladder pressure over time (i.e., course ofa day) or more generally, the anatomical environment/hydrostaticaverage. This can be approximated as the average detrusor pressure,which, in a normal or healthy bladder is between about 6 to 15 cm H₂O.

P_(dissolved-gases)=The total gas tension of bladder urine. As discussedherein, nitrogen is not metabolized by the body and can be ignored inthe above equation because the partial pressure of nitrogen in theatmosphere can be assumed to be approximately equal to the partialpressure of nitrogen in the body, including in the urine within thebody. In much the same way, as the other gases in atmospheric aircomprise only about 1% of the air, they can be ignored as imparting onlya negligible effect. However, unlike nitrogen, oxygen is metabolized bythe body. And, unlike the other gases in atmospheric air, e.g., the 1%,oxygen comprises a comparatively large percentage of the air. Therefore,the differential between the body's partial pressure of oxygen, e.g.,oxygen saturation, and the atmospheric partial pressure of oxygen cannotbe neglected as negligible. Therefore, the partial pressure of dissolvedgases can be approximated as the partial pressure deficit of oxygen. Thepartial pressure of oxygen in the urine is normally about 54-120 cm H₂Oand the partial pressure of oxygen in the atmosphere is normally about216 cm H₂O; consequently an approximate partial pressure deficit ofoxygen is about 100 cm H₂O.

P_(skin tension)=The inward force exerted by the skin of the balloon.

FIG. 15 illustrates a simplified graph of gas volume versus time forpotential balloon loading scenarios (e.g., three different ratios oftotal internal loads to total external loads). The middle, solid line,represents a balloon having a total internal vapor pressure that isequal to the total external forces. When the total external loads areequal to the total internal loads, the balloon with neither shrink norexpand, e.g., the gas volume remains constant because the balloon is atequilibrium. The lower dashed line represents a balloon having a totalinternal vapor pressure that is less than the total external forces.When the total external loads on the balloon are greater than the totalinternal vapor pressure, the gas volume of the balloon will decreaseover time. Finally, the upper dashed line represents a balloon having atotal internal vapor pressure that is greater than the total externalforces. When the total external loads on the balloon are less than thetotal internal vapor pressure, the gas volume of the balloon willincrease over time.

The vapor pressure of the gases contained within the balloon, e.g., PFC,relative to the “load” exerted on the gas in the balloon determines thestability of the balloon's volume. As applied to a balloon implantedwithin the body, e.g., within the bladder, maintaining a substantiallyconstant volume can be desirable. As discussed herein, increasing volumeof the balloon can sometimes be undesirable. For example, overlyincreasing the balloon volume can compromise the balloon, causing it tobecome unstable, plastically deform, and experience other, undesirable,effects. In much the same way, decreasing the volume can cause beundesirable under certain circumstances. For example, overly decreasingthe balloon volume can decrease the attenuating effects of the balloonand can allow the underinflated balloon to settle in the trigone regionof the bladder, causing discomfort to the patient, among other,undesirable, effects.

One or more environmental conditions can affect the force balance ofEquation (8) and, consequently, the performance of an implanted balloon.For example, the partial pressure of oxygen in the atmosphere iselevation dependent. High elevations can have a number of effects on apressure attenuation device. For example, a pressure attenuation devicecould expand comparatively rapidly when exposed to increasinglyelevation. Expansion can be due, among other things, to the wall of theballoon being too weak to limit growth of the device. As the wall of theinflatable implant expands, it can thin, e.g., it can thinsignificantly. Thinning of the membrane wall can compromise theintegrity of the balloon. For example, when the membrane wall is thinnedsufficiently it can lose its ability to elastically deform and canplastically deform. Plastic deformation of the balloon can deleteriouslyaffect the ability of the device to attenuate transient pressure waves.The thinning of the membrane can increase the permeability of themembrane to both gas and liquid, resulting in the increased exchange orloss of gas and/or liquid, potentially reducing the stability of theballoon or the longevity of the balloon in a patient. Furthermore, athigher elevations, increasing volumes of air components can be “pulled”out of the inflatable implant, leaving the PFC. In this case, when morethan one PFC is used (e.g., when, as discussed herein, more than one PFCis used to “tailor” (i.e. “program”, “determine”, or “set”) the vaporpressure), the higher vapor pressure component(s) will be lost at ahigher rate than the lower vapor pressure components(s). One or more ofthese factors can contribute to reduction in implant volume, which cancorrespond to decreased efficacy.

As discussed herein, the partial pressure oxygen deficit is dependent onthe partial pressure of oxygen in the atmosphere. Therefore, Equation(8) is dependent on elevation. While small elevational changes can haveonly negligible effects on Equation (8) and balloon performance, largeelevational changes can have more serious consequences. Consider thefollowing elevational data provided for sea level, 5000 ft highelevation, and on an airplane.

Location Sea Level High Elevation Airplane Elevation 0 ft 5000 ft 8000ft Atmospheric 1030.0 cm H₂O 888.5 cm H₂O 792.5 cm H₂O Pressure pN₂ 79%813.7 cm H₂O 701.9 cm H₂O 626.1 cm H₂O pO₂ 21% 216.3 cm H₂O 186.6 cm H₂O166.4 cm H₂OAs can be seen, the partial pressure of oxygen at 5000 ft high elevationis 29.7 cm H_(high elevation) O less than the partial pressure of oxygenat sea level. And, the partial pressure of oxygen in an airplane at 8000ft is 49.9 cm H2O less than the partial pressure of oxygen at sea level.

Based on Equation (8), to achieve equilibrium at 5000 ft high elevation,either the external forces on the balloon must be increased or theinternal forces (e.g., the internal vapor pressure) must be decreased.In some situations, a gas and/or liquid having a lower vapor pressurewhen implanting the device, e.g., for a resident living at 5000 ft. highelevation.

Changing the vapor pressure of the gases internal to the balloon canleave the balloon appropriate for higher elevations, but inappropriatefor lower elevations, such as sea level (e.g., the balloon canimpermissibly shrink because of the increased pressures at sea level).In some embodiments, should the balloon pressure become less than 0, theballoon can lodge into the trigone area of the bladder and become anirritant and negatively impact the patients ability to tolerate theballoon.

Beyond the variabilities that elevation increase can impose on theinflatable implants disclosed herein, one aspect of the presentdisclosure is that the partial pressure of oxygen in the urine, e.g.,the pO₂ deficit, can contribute to system variability. The pO₂ of urineprovided herein is, for simplicity's sake, frequently stated as 116 cmH₂O. However, the literature reports that, due to numerous factors(e.g., environmental and/or physiological factors, among others) thepartial pressure of oxygen in the urine ranges from about 50 to about120 cm H₂O. Some factors that can change, e.g., increase or decrease,the partial pressure of oxygen in the urine include: hydration, diet,kidney function, general health, and acute elevation changes. Forexample, air travel from seal level can increase the deficient partialpressure imbalance of oxygen by about 22 cm H₂O after about 6 hours atelevation due to the change in partial pressure of oxygen in theatmosphere. Therefore, a pressure attenuation device that can adapt orcompensate for variations, e.g., minor variations or major variations,in the partial pressure imbalance of oxygen in the urine can bedesirable. In certain embodiments of the device and balloon disclosedherein, this deficient partial pressure imbalance of oxygen due to achange of partial pressure of oxygen in the atmosphere can be addressedby programming or setting the skin tension of the balloon in a range ofelevations.

Average detrusor pressure is another variable that can vary from patientto patient. As discussed herein, the walls of the bladder, through theirmuscle tone and mass, exert force on the urine inside, resulting intypical pressures that can be around 15 cm H₂O greater than atmosphericin some patients. And, for the sake of simplifying discussion, thatvalue is used herein as a rough approximation of average bladderpressure. However, average detrusor pressure can vary. For example, insome patients the average detrusor pressure can be 20 cm H₂O, 19 cm H₂O,18 cm H₂O, 17 cm H₂O, 16 cm H₂O, 15 cm H₂O, 14 cm H₂O, 13 cm H₂O, 12, 11cm H₂O, 10 cm H₂O, 9 cm H₂O, 8 cm H₂O, 7 cm H₂O, 6 cm H₂O, 5 cm H₂O, or4 cm H₂O.

In light of the above, an improved pressure attenuation device and/orballoon according to embodiments of the present disclosure can haveballoon skin tension and balloon vapor pressure sufficient to meet asufficient range of the variable conditions described above. Forexample, Table 7, below shows characteristics of a balloon (e.g., skintension and balloon vapor pressure) according to certain embodimentsthat would be sufficient for the lower and upper values, e.g., averageor reasonable lower and upper values, of elevation, pO₂, and averagedetrusor pressure of a wide range of conditions.

TABLE 7 Representative Pressure Attenuation Device Operating Ranges SeaLevel Sea Level 5000 ft Airplane Low pO₂ High pO₂ High pO₂ High pO₂Urine Urine Urine Urine External Loads PO₂ ATM 216 cm H₂O 216 cm H₂O 186cm H₂O 166 cm H₂O PO₂ Urine 80 cm H₂O 100 cm H₂O 100 cm H₂O 115 cm H₂O →PO₂ Deficit 136 cm H₂O 116 cm H₂O 86 cm H₂O 51 cm H₂O P_(Bladder-avg) 15cm H₂O 6 cm H₂O 6 cm H₂O 6 cm H₂O Skin Tension 9 cm H₂O 38 cm H₂O 68 cmH₂O 103 cm H₂O of balloon Tot. External 160 cm H₂O 160 cm H₂O 160 cm H₂O160 cm H₂O Internal Pressure Vapor Pressure 160 cm H₂O 160 cm H₂O 160 cmH₂O 160 cm H₂O of Pfc? Total Internal 160 cm H₂O 160 cm H₂O 160 cm H₂O160 cm H₂O Total. 0 cm H2O 0 cm H2O 0 cm H2O 0 cm H2O Combined(equilibrium) (equilibrium) (equilibrium) (equilibrium)Ranging from seal level low urine pO₂ to airplane high urine pO₂, thetotal environmental load on the implant, including the average detrusorpressure and the PO₂ deficit ranges from about 57 cm H₂O to about 151 cmH₂O. In situations where 120 cm H₂O PFC is used, the balloon coulddeflate when the patient is at sea level with or without low PO₂. Aswill be explained below, increased vapor pressure can be used to createhigher skin tensions which can advantageously allow the balloon toremain inflated at sea level.

Various modifications to the pressure attenuation devices disclosedherein can be made to account for or compensate for both patient andenvironmental variabilities. For example, the balloon may be inflatedwith an inflation media. The inflation media may include a fluid at bodytemperature (37 degrees Celsius) and in certain embodiments the fluidmay be one or more high vapor pressure media that may serve as apressure regulator to help keep device 17 inflated. The one or more highvapor pressure media may be, for example, one or more liquidperfluorocarbons (PFCs), preferably one or more liquid PFCs having avapor pressure greater than 50 Pa. The one or more liquid PFCs maycomprise a perfluorinated heptane, a perfluorinated octane, or one ormore combinations thereof. In certain embodiments, the one or moreliquid PFCs are a mixture of perfluoroheptane and perfluorooctane. Insome embodiments, in addition to the high vapor pressure media, theinflation media can include other gasses in addition to the high vaporpressure media such as air, nitrogen, oxygen, argon, hydrogen, oxygen,helium, carbon dioxide, neon, krypton, xenon, radon, and etc. In certainembodiments, the high vapor pressure media inside the balloon, e.g., thePFC, can be increased, the permeability of the balloon can be decreasedto slow intra-day volume changes, and/or the pressure/volumerelationship of the balloon can be changed via skin tension. In someembodiments, the high vapor pressure media inside the balloon, e.g., thePFC, can have vapor pressure from 155-185 cm H₂O in one embodiment, from155-175 cm H₂O, in another embodiment, from 155-165 cm H₂O in anotherembodiment and from 157-163 cm H₂O in another embodiment 160 cm H₂O inanother embodiment 151-165 cm H₂O. The vapor pressure values discussedand claimed herein are gauge pressures measured at sea level at atemperature of 37° C. In some embodiments, the ranges of the vaporpressure of the high vapor pressure media inside the balloon describedin this paragraph can be combined with the ranges, values and/orfeatures of the balloon described herein such the natural balloonvolume, percent increases in volume when the pressure within the balloonis increased a certain amount, wall thickness of the balloon, and/or theelastic deformation range of the balloon. Advantageously, vaporpressures within these ranges can be used to create higher skin tensionswhich can advantageously allow the balloon to remain inflated at sealevel.

FIG. 16 shows the equivalent attenuation PV curve, e.g., pressure versusvolume, for an embodiment of an embodiment of a pressure attenuationdevice subjected a 140 cm H₂O pulse. As illustrated, a pressureattenuation device can achieve an equivalent attenuation at higherinternal pressures if the volume of the pressure attenuation device isincreased at the high internal pressures. According, in certainembodiments, the volume of the balloon of the pressure attenuationdevice advantageously increases with increasing internal pressure.

As noted above, the high vapor pressure media within the balloon can beformed of various components having the desired vapor pressures. In oneembodiment it can comprise one or more PFCs that can be combined to forma liquid mixture with a particular vapor pressure according to theirmole fraction in the liquid. The one or more liquid PFCs may comprise aperfluorinated heptane, a perfluorinated octane, or one or morecombinations thereof. The one or more liquid PFCs can be a mixture ofperfluoroheptane and perfluorooctane. For example, in some embodiments amixture of about 0.193 mole perfluorooctane and about 0.807 moleperfluoroheptane can result in a vapor pressure of around 160 cm H₂O at37° C. In another example, a mixture of about 0.1 mole perfluorooctaneand 0.9 mole perfluoroheptane can result in a vapor pressure of about170 cm H₂O. In some embodiments, the balloon can be inflated with and/oralso contain other gasses in addition to the high vapor pressure mediasuch as air, nitrogen, oxygen, argon, hydrogen, helium, carbon dioxide,neon, krypton, xenon, radon, and etc.

FIG. 14, which was discussed above, shows an example balloon internalpressure versus balloon volume curve. Balloon internal pressure versusballoon volume curves (P/V) can be useful to characterize theperformance of attenuating balloons. As shown by region A in FIG. 14,balloon P/V curves generally begin with an initial, relativelyhorizontally flat region where the balloon is in a “bag” like state. Theinitial flat region corresponds to the initial filling of the balloonbefore the wall of the balloon begins to apply any load to the fluidsinside the balloon. As shown by region B in FIG. 14, the point at whichthe initial flat region increases sharply corresponds to the balloon'sinitial volume or natural volume. The pressure increases rapidly afterthe initial volume because that is the point at which the balloon wallbegins to impart a load, e.g., the load imparted by the balloon wallchanges from effectively zero to a positive value. As shown by region Cin FIG. 14, after reaching their initial volume, the balloons continueto grow in volume. Because the balloon wall is applying inward forces onthe fluids within the balloon, the pressures increase relatively quicklyafter the initial volume has been exceeded. Depending on thecharacteristics of the balloon, including thickness, stiffness, balloonshape, balloon volume, etc., the balloon will have a range of volumes inwhich its wall changes size elastically without plastic deformation.Elastic deformation allows the balloon to shrink, elastically, if thepressure decreases. As shown by region C in FIG. 14, the elastic regionof the curves has a relatively constant slope, e.g., the slope does notvary significantly from a given value. Most materials have a finiteamount of elastic deformation after which they deform plastically, e.g.,they do not regain (e.g., fully regain), their original shape after thedeforming force is removed. As shown by region D in FIG. 14, thebeginning of the plastic deformation region is frequently where theslope of the line changes markedly and remains substantially constant.After the plastic region is reached, the balloon will likely fail toshrink once the deforming force is removed. An aspect of the presentdisclosure is the recognition that plastic deformation is generallyundesirable in the context of inflatable pressure attenuators, whereaselastic deformation is generally desirable in the same context.

Operating within an elastic deformation range can be desirable for apressure attenuation device. This is because elastic deformation allowsthe implant to adapt to increased forces, whether inside the balloon oroutside the balloon, then regain its original configuration after theforces decrease to their original levels. Therefore, the elastic regioncan be considered to encompass the device's operating range. Balloonembodiments having elastic regions encompassing larger ranges of volumesand larger pressures may be desirable as such balloons may be able towithstand a broader range of environmental changes.

Balloon P/V curves may be characterized, at least partially, by thepercentage of volumetric change for a given change in internal pressurewithin the balloon. For example, certain balloon embodiments increase bysome non-zero volume (by comparison to its natural volume) when thepressure within the balloon is increased from 2.5 cm H₂O, e.g.,transition from a bag to the balloon's natural volume, to a greaterpressure. FIG. 17 illustrates P/V curves 1701 of embodiments of aballoon according certain embodiments of the pressure attenuationdevices. Curve 1 1702, curve 1704, curve 1706, and curve 1708 representdifferent embodiments of balloons that can remain elastic betweeninternal pressures of 2.5 cm H₂O to at least 90 cm H₂O and can have P/Vcurves according to certain embodiments. In addition, the balloonsaccording to these embodiments can be inflated with a high vaporpressure media within the pressure ranges described herein. The balloonpressures discussed herein and also claimed (also referred to as“internal pressure” or “internal balloon pressure” or “pressure withinthe balloon” are gauge pressures measured at sea level at a temperatureof 37° C.

With reference to FIG. 17, in some embodiments, of a pressureattenuation device, the balloon increases in volume when the internalpressure within the balloon is increased from 2.5 cm H₂O to 15 cm H₂O byless than 10%, less than 9.5%, less than 8%, less than 7%, less than5.5%, or less than 4%,. In some embodiments, the balloon increases involume when the internal pressure within the balloon is increased from2.5 cm H₂O to 15 cm H₂O by between 3-10%, between 4.0-9.5%, between4.5-8%, between 4.5-7.0% or about 5%. Within these ranges, the balloonpreferably elastically expands and does not plastically deform. Incertain embodiments, within these ranges, the balloon can elasticallyexpand between 2.5 to 15 cm H₂O for at least 15 cycles, 25 cycles, 50cycles, 100 cycles, or greater. In certain embodiments, these ranges ofpercent increases in volume when the internal pressure within theballoon is increased a certain amount, can be combined with the rangesof vapor pressures for the high vapor pressure media inside the balloondescribed above, the values and/or features of the balloon describedbelow such as the natural balloon volume, wall thickness of the balloon,and/or the elastic deformation range of the balloon.

In some embodiments, the balloon increases in volume when the internalpressure within the balloon is increased from 2.5 cm H₂O to 20 cm H₂O byless than 15%, less than 13%, less than 12%, less than 11%, less than10%, less 8%, less than 6%, or less than 5%. In some embodiments, theballoon increases in volume when the internal pressure within theballoon is increased from 2.5 cm H₂O to 20 cm H₂O by between 4-13%,between 5-12.%, between 6-11%, between 6.5-10% or between 6.5 and 8%, .Within these ranges, the balloon preferably elastically expands and doesnot plastically deform. In certain embodiments, within these ranges, theballoon can elastically expand between 2.5 to 20 cm H₂O for at least 15cycles, 25 cycles, 50 cycles, 100 cycles, or greater. In certainembodiments, these ranges of percent increases in volume when theinternal pressure within the balloon is increased a certain amount, canbe combined with the ranges the vapor pressures for the high vaporpressure inside the balloon described above, the values and/or featuresof the balloon described herein such as additional ranges of percentincreases in volume when the pressure within the balloon is increased acertain amount, the natural balloon volume, wall thickness of theballoon, and/or the elastic deformation range of the balloon.

In some embodiments, the balloon increases in volume when the internalpressure within the balloon is increased from 2.5 cm H₂O to 30 cm H₂O byless than 25%, less than 22.5%, less than 19%, less than 16%, less than12%, or less than 11%. In some embodiments, the balloon increases involume when the internal pressure within the balloon is increased from2.5 cm H₂O to 30 cm H₂O by between 10-25%, between 11-22.5%,between12-19 cm H₂O, or between 13-16 cm H₂O. In certain embodiments, withinthese ranges, the balloon can elastically expand between 2.5 to 30 cmH₂O for at least 15 cycles, 25 cycles, 50 cycles, or 100 cycles. Withinthese ranges, the balloon preferably elastically expands and does notplastically deform. In certain embodiments, within these ranges, theballoon can elastically expand between 2.5 to 30 cm H₂O for at least 15cycles, 25 cycles, 50 cycles, 100 cycles, or greater. In certainembodiments, these ranges of percent increases in volume when theinternal pressure within the balloon is increased a certain amount, canbe combined with the ranges of vapor pressures for the high vaporpressure media inside the balloon described above, the values and/orfeatures of the balloon described herein such as additional ranges ofpercent increases in volume when the pressure within the balloon isincreased a certain amount, the natural balloon volume, wall thicknessof the balloon, and/or the elastic deformation range of the balloon.

In some embodiments, the balloon increases in volume when the internalpressure within the balloon is increased from 2.5 cm H₂O to 40 cm H₂O byless than 45%, less than 40%, less than 30%, less than 27%, less than19%, or less than 15%. In some embodiments, the balloon increases involume when the internal pressure within the balloon is increased from2.5 cm H₂O to 40 cm H₂O by between 10-45%, between 15-40%, between18-30%, or between 19-27%. Within these ranges, the balloon preferablyelastically expands and does not plastically deform. In certainembodiments, within these ranges, the balloon can elastically expandbetween 2.5 to 40 cm H₂O for at least 15 cycles, 25 cycles, 50 cycles,100 cycles, or greater. In certain embodiments, these ranges of percentincreases in volume when the internal pressure within the balloon isincreased a certain amount, can be combined with the ranges vaporpressures for the high vapor pressure media inside the balloon describedabove, the values and/or features of the balloon described herein suchas additional ranges of percent increases in volume when the pressurewithin the balloon is increased a certain amount, the natural balloonvolume, wall thickness of the balloon, and/or the elastic deformationrange of the balloon.

In some embodiments, the balloon increases in volume when the internalpressure within the balloon is increased from 2.5 cm H₂O to 70 cm H₂O byless than 150%, less than 100%, less than 90%, less than 75%, less than60%, less than 55%, less than 45%, or less than 40%. In someembodiments, the balloon increases in volume when the internal pressurewithin the balloon is increased from 2.5 cm H₂O to 70 cm H₂O by between20-150%, between 30-100%, between 40-90%, between 40-75%, between 45-60%or between 50-55%. Within these ranges, the balloon preferablyelastically expands and does not plastically deform. In certainembodiments, within these ranges, the balloon can elastically expandbetween 2.5 to 70 cm H₂O for at least 15 cycles, 25 cycles, 50 cycles,100 cycles, or greater. In certain embodiments, these ranges of percentincreases in volume when the pressure within the balloon is increased acertain amount, can be combined with the ranges of vapor pressures forthe high vapor pressure media inside the balloon described above, thevalues and/or features of the balloon described herein such asadditional ranges of percent increases in volume when the pressurewithin the balloon is increased a certain amount, the natural balloonvolume, wall thickness of the balloon, and/or the elastic deformationrange of the balloon.

In some embodiments, the balloon increases in volume when the internalpressure within the balloon is increased from 2.5 cm H₂O to 90 cm H₂O byless than 190%, less than 100%, less than 90%, or less than 85%, lessthan 70%. In some embodiments, the balloon increases in volume when theinternal pressure within the balloon is increased from 2.5 cm H₂O to 90cm H₂O by at least 10% but less than 90%, or by between 50-190%, between60-150%, between 65-100%, between 75-90% or between 80-85%. Within theseranges, the balloon preferably elastically expands and does notplastically deform. In certain embodiments, within these ranges, theballoon can elastically expand between 2.5 to 90 cm H₂O for at least 15cycles, 25 cycles, 50 cycles, or 100 cycles or greater. In certainembodiments, these ranges of percent increases in volume when thepressure within the balloon is increased a certain amount, can becombined with the ranges vapor pressures for the high vapor pressuremedia inside the balloon described above, the values and/or features ofthe balloon described herein such as additional ranges of percentincreases in volume when the pressure within the balloon is increased acertain amount, the natural balloon volume, wall thickness of theballoon, and/or the elastic deformation range of the balloon.

In certain embodiments, the balloon for the pressure attenuation devicefor the bladder may be characterized by their ability to inflate, staybelow a certain volume, withstand certain pressures, and withstandcertain pressure changes while remaining elastically deformable, allwhile appropriately attenuating the transient pressure event, asdiscussed elsewhere herein.

As discussed herein, bag-like inflatable implants, e.g., implants belowtheir natural volume, can be undesirable due to their potentially lowtolerability. The balloons of certain embodiments the pressureattenuation devices disclosed herein will have varying volumes based onthe balance of forces, e.g., internal forces vs. external forces. Therange of volumes may be bounded by the balloon natural volume on thelower end (as volumes below the natural volume, in which the implant is“bag-like” may be undesirable) and bounded by the inflatable implant'smaximum volume on the upper end.

In some embodiments, the balloon of the pressure attenuation device ofthe embodiments described above, has a natural volume in certainembodiments of between 0.1 and 500 cc, in certain embodiments between 1and 180 cc, in certain embodiment, between 10 and 60 cc. In certainembodiments, the balloon has a natural volume of between 25-30 ml,between 20-35 ml, between 22.5-32.5 ml, or 27 ml. In certainembodiments, these ranges of natural volume can be combined with thepercent increases in volume when the internal pressure within theballoon is increased a certain amount and/or the ranges of vaporpressure of the high vapor pressure media described above and/or thewall thickness of the balloon, and/or the elastic deformation ranges ofthe balloon embodiments described herein. It is also anticipated that incertain embodiments, more than one pressure attenuation device can beused within the bladder and/or pressure attenuation device with morethan one balloon can be used within the bladder. In such embodiments,the total volume of the more than one pressure attenuation device and/ormore than one balloon can be within the natural volume ranges describedabove.

In certain embodiments, the maximum volume of the balloon of thepressure attenuation device, advantageously is no more than 10% of thevolume of the patient's bladder. This is because if the device gets toolarge, it can occupy too much of the volume of the bladder and diminishits capacity to the point where the patient will need to urinate morefrequently. In some embodiments, the maximum volume of the ballooncompared to the volume of the patient's bladder should be less than 50%,less than 45%, less than 40%, less than 35%, less than 30%, less than25%, less than 20%, less than 15%, less than 10%, or less than 5%. Thevolume of an adult bladder is 400-600 ml. Therefore, absolute volumesmay be determined by taking the disclosed percentage of 400-600 ml. Forexample, in an embodiment in which the balloon's maximum volume is lessthan 10%, the absolute maximum volume of the balloon is between 40-60ml.

Balloon maximum value may be a function of several discussed variables,including, but not limited to, partial pressure of oxygen in the urine,balloon internal vapor pressure, elevation, etc. However, the balloonsmaximum volume should be independent of the balloon's natural volume.That is to say, that regardless of the initial, natural volume of theballoon advantageously does exceed the maximum volume value. This isbecause it can be undesirable for the balloon to occupy over a certainthreshold of the bladder's volume due to commensurate decreases in thebladder's functional capacity. For example, given a maximum volume of 50ml: a balloon having a natural volume of 10 ml could in certainembodiments have a maximum operating range of a 10-50 ml; a balloonhaving a natural volume of 20 ml could in certain embodiment have amaximum operating range of 20-50 ml, a balloon having a natural volumeof 30 ml could have in certain embodments a maximum operating range of30-50 ml; etc.

Certain embodiments of the balloon 1711, 68 discussed herein are able towithstand internal pressures of at least 90 cm H₂O without plasticallydeforming. In certain embodiments, the balloon 1711, 68 is able towithstand internal pressures of at least 100 cm H₂O without plasticallydeforming. In certain embodiments, the balloon 1711, 68 is able towithstand internal pressures of at least 110 cm H₂O without plasticallydeforming. In certain embodiments, the balloon 1711, 68 is able towithstand internal pressures of at least 120 cm H₂O without plasticallydeforming.

In certain embodiments, the balloon can elastically deform when theinternal pressure within the balloon is increased from 0 cm H₂O-90 cmH₂O, from 0 cm H₂O to 100 cm H₂O, and/or from 0 cm H₂O-120 cm H₂O.Within these ranges, the balloon can elastically deform for at least 1cycle, for at least 5 cycles, 25 cycles, 50 cycles, 100 cycles orgreater between the maximum and minimum pressure within these ranges. Incertain embodiments, these ranges wherein the balloon can elasticallydeform can be combined with the ranges of percent increases in volumewhen the pressure within the balloon is increased a certain amountdescribed above and/or can be combined with the ranges of vaporpressures for the high vapor pressure media inside the balloon describedabove, the values and/or features of the balloon described herein suchas the natural balloon volume, and/or the wall thickness of the balloon.

In certain embodiments, when the internal pressure within the balloon isincreased from 0 cm H₂O to 90 cm H₂O, from 0 cm H₂O to 100 cm H₂O,and/or from 0 cm H₂O to 120 cm H₂O for at least 1 cycle, for at least 5cycles, 25 cycles, 50 cycles, 100 cycles or greater between the maximumand minimum pressure within these ranges the volume of the balloon for agiven internal pressure changes within +/−1%, +/−5%, and/or +/−10%. Incertain embodiments, these ranges wherein the volume of the balloonremains remain within a certain range for a given pressure can becombined with the ranges of percent increases in volume when thepressure within the balloon is increased a certain amount describedabove and/or can be combined with the ranges vapor pressures for thehigh vapor pressure media inside the balloon described above, the valuesand/or features of the balloon described herein such as the naturalballoon volume, and/or the wall thickness of the balloon

The ability to withstand a given internal pressure without plasticallydeforming may be a function of how long the balloon is subjected to theincreased internal pressure. In some embodiments, the balloon is able towithstand the pressures disclosed herein without plastic deformation forabout 6 hours. In some embodiments, the inflatable implant is able towithstand the pressures disclosed herein without plastic deformation forat least 12 hours, 24, hours, 36 hours, 48 hours, 60 hours, or 72 hours.In some embodiments, the inflatable implant is able to withstand thepressures disclosed herein without plastic deformation for at least 1week, at least 2 weeks, at least 3 weeks, or at least 4 weeks. In someembodiments, the balloon is able to withstand the pressures disclosedherein without plastic deformation (for at least 2 months, at least 3months, at least 4 months, at least 5 months, at least 6 months, atleast 1 year, at least 2 years, or at least 3 years. In someembodiments, the balloon remains elastic through the ranges discussedherein at after 15, 25, 50, or 100 cycles.

In some embodiments, balloons falling within the P/V performanceparameters and/or plastic deformation disclosed herein also have anincreased internal vapor pressure offset by an increased skin tension,e.g., due to an increased thickness or other material property(ies). Insome embodiments, the balloon's internal vapor pressure is greater than150 cm H₂O. In some embodiments, the balloon's internal vapor pressureis great than 155 cm H₂O, greater than 160 cm H₂O, greater than 165 cmH₂O, greater than 170 cm H₂O, or greater than 175 cm H₂O. In someembodiments, the balloon/s internal vapor pressure is between 155-185 cmH₂O. In some embodiments, the balloon's internal vapor pressure isbetween 155-175 cm H₂O, between 155-165 cm H₂O, or between 157-163 cmH₂O, and in another embodiment about 160 cm H₂O.

The tables below, table 8(A) and 8(B), show the volume and percentchange in volume for various representative balloon embodiments (1),(2), (3), (4), (5), and (6)which are also illustrated in FIG. 17.

TABLE 8(A) Volume for Balloon Embodiments at Set Pressures Pressure (cmH₂O) (1) (2) (3) (4) (5) (6) 2.5 27 ml 25.5 ml 23.5 ml 21 ml 27.5 ml 25ml 15 29.5 ml 27 ml 24.75 ml 22 ml 29.4 ml 26.5 ml 20 30 ml 28 ml 25.25ml 22.5 ml 30 ml 27 ml 30 32.5 ml 30 ml 26.75 ml 23.75 ml 31.5 ml 29.5ml 40 36 ml 32.5 ml 29.4 ml 25.25 ml 33.5 ml 30 ml 70 52 ml 43 ml 36 ml31.25 ml 42 ml 36 ml 90 70 ml 54 ml 43 ml 35.5 ml 51 ml 42 ml

TABLE 8(B) % Volume Change Compared to Initial Volume at 2.5 cm H2OPressure (cm H₂O) (1) (2) (3) (4) (5) (6) 2.5  0%  0%  0%  0%  0%  0% 15 9%  6%  5%  5%  7%  6% 20 11% 10%  7%  7%  9%  8% 30 20% 18% 14% 13%15% 18% 40 33% 27% 25% 20% 22% 20% 70 93% 69% 53% 49% 53% 44% 90 159% 112%  83% 69% 85% 68%

In some embodiments, the balloon does not burst when its internalpressure is less than or equal to 90 cm H₂O, less than or equal to 70 cmH₂O, cm H₂O, less than or equal to 40 cm H₂O, less than or equal to 20cm H₂O, or less than or equal to 10 cm H₂O.

In some embodiments, the inflatable balloon can also have relatively lowdeflection values and have high burst test pressures. Table X belowprovides example data of deflection and test pressures at differentvolumes and pressures of cm H₂O for two different embodiments of aballoon of a pressure attention device (with the first 4 rows of Table Xcorresponding to one embodiment and the second 4 rows of the Table Xcorresponding to a second embodiment). The deflection and test pressuresof Table X can be determined on a balloon using the test fixture andprocedures described in paragraphs [0457] to [0465] and FIGS. 146-153 ofU.S. Patent Publication 2015/0216644, the entirety of which is herebyincorporated by reference herein for all purposes and included in thisapplication. As indicated in the table below, in some embodiments, theballoon can withstand a test pressure of at least 15 cm H₂O and/or 20 cmH₂O without bursting and/or having a minimum deflection of 6 mm or lessand/or 5 mm.

TABLE X Pressure and Test Pressure Characteristics Volume PressureDeflection Bt Test Pressure ml cmH20 mm cmH20 27 20 6 35 no burst 30 406 27 no burst 36 70 6 26 no burst 42 <90 5 31.25 no burst 30 20 5 25 noburst 34 40 5 74 no burst 42 <70 5 28 no burst 42 <70 5 24 no burst

Table 9, below, provides data for three different embodiments of aballoon of an embodiment of the pressure attenuation device. Of course,while certain parameters are shown, one or more parameters may bechanged. Within these parameters, the balloon preferably elasticallyexpands and does not plastically deform.

TABLE 9 Example Balloon Characteristics Performance Attribute Embodiment1 Embodiment 2 Embodiment 3 Natural Volume 26 ml 28 ml 25-29 ml (roomtemp.) Inflated Volume 30 ± 2 ml 30 ± 2 ml (room temp.) Wall Thickness0.00205- 0.00210- 0.002- (2x) 0.00325 inches 0.00315 inches 0.0035inches Volume 27 ml 30 ml 26-31 ml Observed at 20 cm H₂O Volume 36 ml 43ml 35-44 ml Observed at 70 cm H₂O Volume 42 ml 51 ml 41-52 ml Observedat 90 cm H₂O Pressure 0.67-0.78 psi 0.60-0.75 psi 0.5-0.9 psiAttenuation at 2 psi Volume after 67 27 ml 30 ml 25-30 m days At 140 cmH₂O

Limiting Implant Expansion

In another embodiment two or more PFCs with different vapor pressuresare mixed to give an average vapor pressure based on the mole fractionof the components. As the PFC mixture diffuses out of the device overtime the more volatile component will diffuse proportionately to itsmole fraction in the mix, therefore the mole fraction of the highervapor pressure component will go down and the vapor pressure of the mixwill likewise be reduced. This phenomenon could be used to control theultimate size of the balloon. As the balloon expands, the vapor pressureof the PFC mix will go down placing an upper limit on balloon volume.

In some embodiments, the skin tension of the balloon could be usedadvantageously to limit balloon expansion. As the balloon expands, thetension of the balloon material will increase until the excess gaspressure in the balloon will be offset by the tension in the balloonskin.

In addition, just as skin geometries and other features of the implant66 can change the V/P curve; these same or similar features can limitexpansion, deflation or the rate of change of the implant.

In some embodiments, an implant has a high surface to volume ratio toaffect a rapid rate of change. The implant shape can be selected fromcylindrical, spiral, or ridged. In another embodiment a slow rebound orrapid inflation is desired and thus a low surface area to volume ratiois desired and a spherical design is selected.

In a further embodiment the quantity of PFC in a balloon could be usedto limit expansion. A precise quantity of PFC could be added to theballoon such that as the balloon expands the PFC would volatilize tomaintain its partial pressure until the PFC liquid reservoir isdepleted. The PFC gas would then dilute with further expansion and theinternal pressure of the balloon would be limited.

Devices described herein containing PFC and other gases can be placedinto pressure equilibrium with the environment in which they aredeployed. Since no natural environment is truly at constant pressure,the balloon system would need to gain external gases during low externalpressure times and lose gas during high pressure times. The loss of gaswould need to balance with the gain of gas for long term stability.

Delivery of Implant and Removal of Implant

As noted above, the pressure attention devices 12, 66 according to theembodiments described herein can be transurethrally deployed into thebladder in its first configuration, and enlarged to its secondconfiguration once positioned within the bladder to accomplish apressure attenuation function. Preferably, a crossing profile, or agreatest cross-sectional configuration, of the attenuation device 17, 66when in the first configuration is no greater than 24 French (8 mm),and, preferably, no greater than 18 French (6 mm). This can beaccomplished, for example, by rolling a deflated balloon about alongitudinal axis, while the interior chamber is evacuated. Oncepositioned within the bladder, the interior chamber 72 is filled withthe media to produce a pressure attenuation device 17, 66. After acertain period of time, the pressure attention devices 12, 66 can bedeflated and removed from the bladder.

With reference to FIGS. 18A to 26D, further embodiments of devices andmethods are disclosed which can be used to insert and/or remove thepressure attention devices 12, 66 embodiments described herein. Furtherdetails for such insertion and removal devices can be found for example,in the following documents, U.S. Patent Application Publication No.US2015/0216644A1, Cahill et al., published Aug. 6, 2015 and U.S. patentapplication Ser. No. 16/557,555 filed Aug. 30, 2019, the entirety ofthese applications are all incorporated by reference herein for allpurposes.

Delivery Device

The pressure attenuation devices disclosed herein may be delivered to ananatomical structure in a compacted or deflated state and, after beingdelivered to the anatomical structure, may be inflated and deployed.Preferably, the delivery of the device to the anatomical structure in adeflated state is accomplished by positioning device in its deflatedstate within a window of a catheter, with distal end of inflation tubesealed against intermediate section of valve in the manner discussedabove. The balloon may be folded within catheter in a mannercomplementary to the shape of window so as to maximize the likelihoodthat device may be retained within catheter window prior to beinginflated and may be released through window once inflated.

Certain embodiments of a delivery device are described in U.S. PatentApplication Publication No. 2010/0222802, incorporated by referenceherein. See for example: FIGS. 6-18H, and the accompanying discussion,including at paragraphs [0153]-[0206]. Embodiments of a delivery deviceare also provided in U.S. Pat. No. 6,976,950, incorporated by referenceherein. See for example: FIGS. 6-11A, 34A-35B and 48A-48D, and theaccompanying discussion, including at columns 13-16, and 35.

A delivery device 15 may be inserted through the passageway created byan access device. As shown in FIGS. 18A-B, the delivery device 15 may beused to deliver a pressure-attenuating device to the body, such as tothe bladder. The delivery device 15 may deliver the pressure attenuationdevice in a compacted state which may then be inflated and released. Thesteps of inflation and/or release may be performed by the deliverydevice. The delivery device 15 can include a delivery tube, an inflationtube, a connection to inflation media and a release mechanism, amongother features.

Referring now to FIG. 19, there is shown a top view of one embodiment ofa sterilizable kit comprising certain components of a delivery device15, the sterilizable kit being represented generally by referencenumeral 1751.

Kit 1751 may comprise a sheet of support material 1753, which may be asheet of cardboard or a similarly suitable support material. Kit 1751may further comprise a sealed pouch 1755 surrounding support material1753, pouch 1755 defining a sealed cavity 1757. Pouch 1755 may be madeof a transparent material, such as one or more transparent polymersheets. Kit 1751 may further comprise the components of delivery device15 nearly being fully assembled, except that an additional syringe forinflation media is not present and that syringe 1691 is not attached tothe remaining components of delivery device 15. Syringe 1691 may bedisposed within cavity 1757 and may be mounted on support material 1753,and the remainder of delivery device 15 may be disposed within cavity1757 and may be mounted on support material 1753 at a distance fromsyringe 1691. Syringe 1691 may be opened to drawn in a volume of aircorresponding to the volume of air one wishes to dispense therefrom intodevice 17. Although not visible in FIG. 19, kit 1751 may furthercomprise pressure-attenuating device 17, 66, which may be loaded withinwindow catheter 1641 of delivery device 15 and may be coupled toinflation tube 1741 in the manner described above. Kit 1751 may furthercomprise a removable protective sleeve 1759, which may be inserted overcatheter 1641 to ensure retention pressure-attenuating device 17 withincatheter 1641 during shipping and/or storage. (Sleeve 1759 is removedfrom catheter 1641 prior to use; alternatively, sleeve 1759 may bereplaced with cover 1703, which may be retained for use in the mannerdescribed above.) All of the components of kit 1751 are made of amaterial that may be sterilizable by a suitable sterilization technique,such as gamma radiation.

An advantageous feature of kit 1751 is that the air contained withinsyringe 1691 may become sterilized during the sterilization procedureapplied to kit 1751. In this manner, one may minimize the introductionof air into pressure-attenuating device 17 that may contain undesirablemicroorganisms. For similar reasons, microbial filters may alternativelyor additionally be appropriately positioned within fluid connector 1423and/or check valves 1441 and 1443.

Referring now to FIG. 20, the pressure-attenuating device 17 is shown ina deflated, flattened state with internal retention member 1715 on thelower layer of the balloon prior to being folded. A plurality ofimaginary fold lines 1741-1, 1741-2, and 1741-3 are shown on balloon1711 to depict where balloon 1711 may be folded. According to oneembodiment, balloon 1711 may first be folded about line 1741-1, thenabout line 1741-2, and then about line 1741-3. Alternatively, balloon1711 may be folded about line 1741-2, then about line 1741-1, and thenabout line 1741-3. When device 17 is inflated, balloon 1711 may unfoldin an order opposite to the order in which it had previously beenfolded. In an alternate embodiment, the balloon includes an integralretention member 1715, which is on top of the balloon when folded alongline 1741-1 described above. The integral retention member may becircular, rectangular, oval or any shape so long as it is sufficientlywide to extend beyond the opening in the window, more preferably greaterthan 1.5 times the opening in the window, more preferably two times theopening in the window. This dimension permits the retention member to betucked under the catheter on one or more sides of the window when thefolded balloon is secured in the catheter.

It is to be understood that, although pressure-attenuating device 17 hasbeen described herein as being inflatable, pressure-attenuating device17 could be expandable in ways other than by inflation. For example,pressure-attenuating device 17 could be self-expandable, for instance,by virtue of being made of a shape-memory material.

Some of the advantageous features of using a delivery device 15 todeliver pressure-attenuating device 17 are that, due to the orientationand placement of window, there is a controlled deployment ofpressure-attenuating device 17 away from the trigone of the patient andpressure-attenuating device 17 is kept away from the walls of thebladder while being inflated, such contact with the walls of the bladderpossibly impeding the opening of valve to inflate device 17.

Referring now to FIG. 21, there is shown a flowchart, schematicallydepicting one possible method 1771 of implanting pressure-attenuatingdevice in an anatomical structure of a patient, such as a bladder.Method 1771 may begin with a step 1771-1 of installing an access device13 in a patient in any of the manners discussed above. Where, forexample, an access device is used to provide transurethral access to thebladder, said installing step may comprise inserting a distal end ofobturator, covered by sleeve 181, through the urethra 182 and into thebladder 183 and then removing obturator, whereby an access pathextending across the urethra and into the bladder may be created (seeFIG. 21A). Method 1771 may then continue with a step 1771-2 of insertinga distal end of a delivery device 15 through the access device 13 andinto the anatomical structure of a patient. This may be done byinserting distal end of delivery device 15 through the remaininginstalled portion of access device 13 and into the bladder of thepatient (see FIG. 21B). (Prior to insertion of delivery device 15 intoan access device 13, pressure-attenuating device 17 may be loaded intodelivery device 15.)

Method 1771 may then continue with a step 1771-3 of inflatingpressure-attenuating device 17 (see FIG. 21C). Said inflating step maybe effected by fully a depressing piston to dispense a first fluidmedium from a first syringe into pressure-attenuating device 17 and thenby fully a depressing piston to dispense a second fluid medium from asecond syringe into pressure-attenuating device 17. Method 1771 may thencontinue with a step 1771-4 of releasing pressure-attenuating device 17from delivery device 15 (see FIG. 21D), thereby allowing device 17 tofloat freely in the bladder or other anatomical structure. Saidreleasing step may be affected by a deactivating safety and then by asqueezing trigger, thereby causing a push-off member to slide distallyuntil a push-off member pushes device 17 off of a distal end of aninflation tube. Method 1771 may then proceed with a step 1771-5 ofwithdrawing the delivery device from the access device 13. This may bedone by withdrawing delivery device 15 from the remaining installedportion of an access device 13 while holding the remaining installedportion of access device 13 stationary in the patient. (Access device 13may thereafter be removed from the patient or may remain in the patientto provide a conduit through which observational, removal, or otherdevices may be inserted.)

Removal

A removal device may be inserted through the passageway created by anaccess device. The removal device may be used to capture, to deflateand/or to remove the pressure-attenuating device. The removal device mayalso be used to view the inside of the anatomical structure, as well asthe pressure-attenuating device. This viewing may be done during all orpart of the capturing, deflating, and/or removing thepressure-attenuating device.

Certain additional embodiments of a removal device are described in U.S.Patent Application Publication No. 2010/0222802, incorporated byreference herein. See for example: FIGS. 19A-22B, 23H, and 24-29C andthe accompanying discussion, including at paragraphs [0207]-[0274].Additional embodiments of a removal device and/or the insertion devicewhich can be in certain arrangements in combination with the embodimentsof a pressure attenuation device herein can also be found in U.S.Provisional Application No. 62/725210, filed Aug. 30, 2018, the entiretyof which is also hereby incorporated by reference herein.

Embodiments of a removal device are also provided in U.S. Pat. No.6,976,950, incorporated by reference herein. See for example: FIGS. 12,and 20-23, and the accompanying discussion, including at columns 18-21,and 25-26.

Referring now to FIG. 22, removal device 19 according to a certainembodiment is shown. The removal device 19 can include a pair ofscissor-like handles that can be used to articulate a pair of jaws 1981,1983 as will be described below. Removal device 19 may further comprisea pair of jaws 1981 and 1983 (FIGS. 23A-D, FIGS. 24A-D, FIGS. 25A-B).FIGS. 25A-B, show jaw 1983 and jaw 1981 assembled on removal device 19.The jaws can include corresponding teeth 1997, 2017 which can be used togrip or secure an implant. The jaws may also include one or more surfacedamaging or compromising structures. For example, the surface damagingstructure 2003, 2023 can be a needle, knife, sharpened tooth, etc. Insome embodiments, the surface damaging structure can be a canulatedneedle that can also serve to allow the media within in the implant toescape or otherwise be removed. In some embodiments, having the openingin the needle extend the entire length of the exposed needle structurepermits the balloon to continue to deflate even when the needle haspenetrated completely through the balloon. Additionally, the orientationof the sharp edge towards the distal end of the grasper has theadvantage of preventing lacerating the balloon film during the tensileremoval of the deflated or partially deflated balloon thru the sheath.Additionally, the proximity of the needle relative to adjacent teeth canimprove the function of the removal system. Specifically, if the spacebetween the tip of the needle and the tip of an adjacent tooth isbetween 0.05 and 10 times the difference in height between the tip ofthe needle and the tip of the adjacent tooth. This distance prevents theballoon from “tenting” over the needle and adjacent teeth without needlepenetration of the balloon.

Jaw 1981, which is also shown separately in FIGS. 23A-D, may comprise anelongated member 1985 (which may be, for example, approximately 1.55-2.5inches in length), preferably made of a medical-grade stainless steel ora similarly suitable material. Member 1985 may be shaped to include aproximal portion 1987 and a distal portion 1989. Proximal portion 1987,which may comprise a generally flat and arcuate arm, may be shaped toinclude a first transverse opening 1991 proximate to a proximal end1987-1 of proximal portion 1987 and a second transverse opening 1993spaced distally a short distance from first transverse opening 1991. Apivot pin 1995 may be received within opening 1991 of proximal portion1987, as well as within opening 1967 of arm 1961, so as to pivotallycouple jaw 1981 to arm 1961. A pivot pin 1996 may be received withinopening 1993 of proximal portion 1987, as well as within opening 1933 ofbracket 1921, so as to pivotally couple jaw 1981 to bracket 1921. Distalportion 1989 of member 1985 may be shaped to include a row of teeth 1997facing towards jaw 1983, the row of teeth 1997 extending proximally fromapproximately the distal end of distal portion 1989. Each tooth 1997 mayextend substantially across the width of distal portion 1989 and mayhave a height of, for example, approximately 1-10 mm, preferablyapproximately 5 mm. Each tooth 1997 may have a dulled peak 1997-1 thathas a radius of, for example, 0.001-0.250 inch, preferably 0.005-0.050inch, more preferably 0.010-0.25 inch. A first transverse opening 1999may be provided in distal portion 1989 amongst teeth 1997, and a secondtransverse opening 2001 may be provided in distal portion 1989 amongstteeth 1997, first and second transverse openings 1999 and 2001 beingspaced apart from one another by a short distance. A cannulated needle2003 may be fixedly mounted in transverse opening 1999, needle 2003having a sharpened end 2003-1 facing towards jaw 1983. Preferably,needle 2003 has a height that exceeds the height of teeth 1997 so thatsharpened end 2003-1 extends beyond dulled peaks 1997-1. Needle 2003 mayhave an inner diameter of, for example, approximately 0.0005-0.500 inch,preferably approximately 0.005-0.250 inch, more preferably approximately0.010-0.050 inch, and may have an outer diameter of, for example,approximately 0.001-0.750 inch, preferably approximately 0.010-0.300inch, more preferably approximately 0.015-0.075 inch.

Jaw 1983, which is also shown separately in FIGS. 24A-D, may comprise anelongated member 2005 (which may be, for example, approximately 1.55-2.5inches in length), preferably made of a medical-grade stainless steel ora similarly suitable material. Member 2005 may be shaped to include aproximal portion 2007 and a distal portion 2009. Proximal portion 2007,which may comprise a generally flat and arcuate arm, may be shaped toinclude a first transverse opening 2011 proximate to a proximal end2007-1 of proximal portion 2007 and a second transverse opening 2013spaced distally a short distance from first transverse opening 2011. Apivot pin 2015 may be received within opening 2011 of proximal portion2007, as well as within opening 1973 of arm 1963, so as to pivotallycouple jaw 1983 to arm 1963. Pivot pin 1996 may be received withinopening 2013 of proximal portion 2007, as well as within opening 1933 ofbracket 1921, so as to pivotally couple jaw 1983 to bracket 1921. Inthis manner, proximal movement of rod 1941, which may be caused bypivotal movement of ring portion 1807 of member 1801 towards ringportion 1823 of member 1803, may cause arms 1961 and 1963 to pivottowards each other which, in turn, may cause jaws 1981 and 1983 to pivottowards each other. On the other hand, distal movement of rod 1941,which may be caused by pivotal movement of ring portion 1807 of member1801 away from ring portion 1823 of member 1803, may cause arms 1961 and1963 to pivot away from one another which, in turn, may cause jaws 1981and 1983 to pivot away from one another. Jaws 1981 and 1983 may open toan angle of, for example, approximately 20-150 degrees.

Distal portion 2009 of member 2005 may be shaped to include a row ofteeth 2017 facing towards jaw 1981. The row of teeth 2017 may bestaggered relative to teeth 1997 so that the peaks 1997-1 of teeth 1997may be aligned with the spaces between teeth 2017 when jaws 1981 and1983 are closed and so that the peaks 2017-1 of teeth 2017 may bealigned with the spaces between teeth 1997 when jaws 1981 and 1983 areclosed. Each tooth 2017 may extend substantially across the width ofdistal portion 2009 and may be shaped and dimensioned similarly to eachof teeth 1997. A first transverse opening 2019 may be provided in distalportion 2009 amongst teeth 2017, and a second transverse opening 2021may be provided in distal portion 2009 amongst teeth 2017. Opening 2019may be appropriately positioned and appropriately dimensioned to receivecannulated needle 2003 of jaw 1981 when jaws 1981 and 1983 are closed.(By receiving the sharpened end 2003-1 of needle 2003, opening 2019facilitates and promotes full closure of jaws 1981 and 1983 around aninflated device 17, as opposed to having needle 2003 be deflected fromthe compressed and inflated device 17.) Opening 2019 may have an innerdiameter of, for example, approximately 0.002-0.100 inch, preferably0.010-0.300 inch, more preferably 0.015-0.100 inch. Opening 2021 may bealigned with opening 2001 of jaw 1981 when jaws 1981 and 1983 areclosed, and a cannulated needle 2023 may be fixedly mounted in opening2021 so as to be receivable within opening 2001 of jaw 1981 when jaws1981 and 1983 are closed. Cannulated needle 2023 may have a sharpenedend 2023-1 facing towards jaw 1981, and needle 2023 and opening 2001 maybe dimensioned similarly to needle 2003 and opening 2019, respectively.

Preferably, teeth 1997 and 2017 are dimensioned appropriately so that,when jaws 1981 and 1983 are closed, a small gap 2018 (seen best in FIG.109(d)) is left between the respective rows of teeth 1997 and 2017 thatenables device 17 to be trapped between teeth 1997 and 2017 whileminimizing any tearing of device 17 by teeth 1997 and 2017. In thismanner, device 17 may be securely held or gripped between teeth 1997 and2017 while cannulated needles 2003 and 2023 puncture device 17.Moreover, because needles 2003 and 2023 are cannulated, the fluidcontents of device 17 may be quickly evacuated from device 17 throughneedles 2003 and 2023 without having needles 2003 and 2023 plug the samepuncture holes they create.

It is to be understood that, although cannulated needles 2003 and 2023are described herein as being used to puncture device 17, otherpuncturing devices, such as, but not limited to, blades, scissors, pins,hooks, or the like, may alternatively or additionally be used.

In addition, it is to be understood that, although cannulated needles2003 and 2023 are described herein as being oriented generallyperpendicular to members 1985 and 2005, respectively, cannulated needles2003 and 2023 need not be so oriented and may be oriented, for example,so that sharpened ends 2003-1 and 2023-1 are angled towards proximalportions 1987 and 2007, respectively.

Additionally, it is to be understood that, although both jaw 1981 andjaw 1983 are described herein as being movable, one could make one ofjaws 1981 and 1983 stationary and the other of jaws 1981 and 1983movable.

Referring now to FIG. 26, there is shown a flowchart, schematicallydepicting one possible method 2051 of using removal device 19 to removean implanted pressure-attenuating device 17 from an anatomical structureof a patient, such as a bladder. Method 2051 may begin with a step2051-1 of installing an access device 13 in a patient in any of themanners discussed above. Where, for example, an access device 13 can beused to provide transurethral access to the bladder, said installingstep may comprise inserting a distal end of an obturator, which may becovered by sleeve, into the urethra 182, advancing the obturator andsheath through the urethra 182 and into the bladder 183, and thenremoving the obturator, whereby an access path extending across theurethra 182 and into the bladder 183 may be created (see FIG. 26A).Method 2051 may then continue with a step 2051-2 of inserting the distalend of a removal device 19 through the access device 13 and into theanatomical structure of the patient. This can be done by inserting thedistal end of removal device 19 through the remaining installed portionof the access device 13 and into the bladder of the patient (see FIG.26B). Where the method 2051 is performed in the bladder, or other fluidfilled structure, the method may then continue with a step 2051-3 ofemptying the structure of liquid, such as through stopcock valve 287,until the inflated pressure-attenuation device 17 comes into alignmentwith removal device 19. For example, urine can be removed from thebladder until the pressure- attenuation device 17 is aligned with openedjaws 1981 and 1983 as observed through a scope (see FIG. 26C). Method2051 may then continue with a step 2051-4 of engaging the inflatedpressure-attenuation device 17 with the removal device 19. This may alsoinclude deflating the inflated pressure-attenuation device 17. Forexample, the jaws 1981 and 1983 can close around pressure-attenuationdevice 17, causing pressure-attenuating device 17 to deflate over thenext several seconds (see FIG. 26D). Method 2051 may then conclude witha step 2051-5 of withdrawing removal device 19, together with thedeflated pressure-attenuating device 17 from the anatomical structurethrough the access device 13. The implanted pressure-attenuating 17 maybe held between jaws 1981 and 1983 and may be removed through theremaining installed portion of access device 13 while the remaininginstalled portion of access device 13 is held stationary in the patient.If, for some reason, pressure-attenuating 17 has not deflated completelyas it is being withdrawn from the patient, the distal end 64 of sheath61 may advantageously serve as a fulcrum to help to compresspressure-attenuating 17 sufficiently for its facile withdrawal from thepatient. (Access device 13 may thereafter be removed from the patient ormay remain in the patient to provide a conduit through whichobservational, removal, or other devices may be inserted.)

Coatings

Despite the hydrophobic tendencies and relative insolubility of PFCs inwater and bodily fluids, PFCs will diffuse out of certain enclosures.This can be minimized by various surface treatments including lubricitycoatings, anti-microbial coatings, acid or basic pH coatings, drugeluting or containing coatings, roughening, or establishing a positivelyor negatively charged surface. Both the interior and/or the exterior ofthe balloons disclosed herein can be treated and each could be treatedin a like or different matter. For example they can be charged + on theoutside and − on the inside or rough on the outside to form and capturebubbles and smooth on the outside to be non-irritating. The inside andoutside of the enclosure can be hydrophilic or hydrophobic,alternatively the inside and outside can be treated to have oppositeattractiveness to water.

Examples of suitable coatings for various devices disclosed hereininclude: aqueous hydrogels on inside to prevent bubble formation, butylrubbers to hold in PFCs, metal coatings, nano-crystallized silver basedantimicrobial coating, polyvinylpryrrolidone based coatings, drugcoatings including duloxetine hydrochloride, neurotransmitters mediatingdrugs, analgesics, antiseptics, antibiotics, incontinence treatmentdrugs, anti-cancer drugs, cystitis treating drug, and oxybutynin.

Initial and Automatic Inflation

Certain embodiments involve the inflation of implants described hereinwith initial infusions of various media, including gases or liquids,such as air, nitrogen, oxygen, carbon dioxide, PFC, etc. The initialinfusion can be before or after the device is implanted. The initialinfusing can be delivered via a syringe, tube, capsule, ampule, cannula,or other delivery device.

In another embodiment, a self-inflating implant comprising a selectedPFC element and an enclosure at least partially permeable to nitrogenand oxygen is provided. After implantation, the PFC vapor will diluteany air component gases within the enclosure and cause the air componentgases in the anatomical structure to diffuse into the enclosure untilequilibrium is reached thereby inflating the enclosure device.

In some embodiments, a pressurized implant is adapted to inflate overtime to a selected volume or pressure and then deflate in response to anelevated pressure. For example, an implant is inserted within a bladderand inflates to a first selected pressure or volume. Upon theapplication of an external load or pressure, such as when the patientvoids the bladder, the implant reaches a second selected pressure, atwhich point the implant is adapted to rapidly decrease in volume as thehigh vapor pressure element within the implant condenses into liquid.When the external load is removed, such as, after the bladder is empty,the implant will gradually return to its first selected volume orpressure. Thus, by providing an implant operable to attenuate bladderpressure spikes within a certain range and then quickly deflate at thetime of voiding, a diminished and more comfortable volume is present atthe time of emptying of the bladder. Therefore, a more comfortabletreatment is effected.

The foregoing description and examples has been set forth merely toillustrate the disclosure and are not intended as being limiting. Eachof the disclosed aspects and embodiments of the present disclosure maybe considered individually or in combination with other aspects,embodiments, and variations of the disclosure. In addition, unlessotherwise specified, none of the steps of the methods of the presentdisclosure are confined to any particular order of performance.Modifications of the disclosed embodiments incorporating the spirit andsubstance of the disclosure may occur to persons skilled in the art andsuch modifications are within the scope of the present disclosure.Furthermore, all references cited herein are incorporated by referencein their entirety.

Terms of orientation used herein, such as “top,” “bottom,” “horizontal,”“vertical,” “longitudinal,” “lateral,” and “end” are used in the contextof the illustrated embodiment. However, the present disclosure shouldnot be limited to the illustrated orientation. Indeed, otherorientations are possible and are within the scope of this disclosure.Terms relating to circular shapes as used herein, such as diameter orradius, should be understood not to require perfect circular structures,but rather should be applied to any suitable structure with across-sectional region that can be measured from side-to-side. Termsrelating to shapes generally, such as “circular” or “cylindrical” or“semi-circular” or “semi-cylindrical” or any related or similar terms,are not required to conform strictly to the mathematical definitions ofcircles or cylinders or other structures, but can encompass structuresthat are reasonably close approximations.

Conditional language used herein, such as, among others, “can,” “might,”“may,” “e.g.,” and the like, unless specifically stated otherwise, orotherwise understood within the context as used, is generally intendedto convey that some embodiments include, while other embodiments do notinclude, certain features, elements, and/or states. Thus, suchconditional language is not generally intended to imply that features,elements, blocks, and/or states are in any way required for one or moreembodiments or that one or more embodiments necessarily include logicfor deciding, with or without author input or prompting, whether thesefeatures, elements and/or states are included or are to be performed inany particular embodiment.

Conjunctive language, such as the phrase “at least one of X, Y, and Z,”unless specifically stated otherwise, is otherwise understood with thecontext as used in general to convey that an item, term, etc. may beeither X, Y, or Z. Thus, such conjunctive language is not generallyintended to imply that certain embodiments require the presence of atleast one of X, at least one of Y, and at least one of Z.

The terms “approximately,” “about,” and “substantially” as used hereinrepresent an amount close to the stated amount that still performs adesired function or achieves a desired result. For example, in someembodiments, as the context may dictate, the terms “approximately”,“about”, and “substantially” may refer to an amount that is within lessthan or equal to 10% of the stated amount. The term “generally” as usedherein represents a value, amount, or characteristic that predominantlyincludes or tends toward a particular value, amount, or characteristic.As an example, in certain embodiments, as the context may dictate, theterm “generally parallel” can refer to something that departs fromexactly parallel by less than or equal to 20 degrees.

Unless otherwise explicitly stated, articles such as “a” or “an” shouldgenerally be interpreted to include one or more described items.Accordingly, phrases such as “a device configured to” are intended toinclude one or more recited devices. Such one or more recited devicescan be collectively configured to carry out the stated recitations. Forexample, “a processor configured to carry out recitations A, B, and C”can include a first processor configured to carry out recitation Aworking in conjunction with a second processor configured to carry outrecitations B and C.

The terms “comprising,” “including,” “having,” and the like aresynonymous and are used inclusively, in an open-ended fashion, and donot exclude additional elements, features, acts, operations, and soforth. Likewise, the terms “some,” “certain,” and the like aresynonymous and are used in an open-ended fashion. Also, the term “or” isused in its inclusive sense (and not in its exclusive sense) so thatwhen used, for example, to connect a list of elements, the term “or”means one, some, or all of the elements in the list.

Overall, the language of the claims is to be interpreted broadly basedon the language employed in the claims. The language of the claims isnot to be limited to the non-exclusive embodiments and examples that areillustrated and described in this disclosure, or that are discussedduring the prosecution of the application.

Although systems and methods for inflatable implants, and pressureattenuating inflatable implants, have been disclosed in the context ofcertain embodiments and examples, this disclosure extends beyond thespecifically disclosed embodiments to other alternative embodimentsand/or uses of the embodiments and certain modifications and equivalentsthereof. Various features and aspects of the disclosed embodiments canbe combined with or substituted for one another in order to form varyingmodes of systems and methods for inflatable implants, and pressureattenuating inflatable implants. The scope of this disclosure should notbe limited by the particular disclosed embodiments described herein.

Certain features that are described in this disclosure in the context ofseparate implementations can be implemented in combination in a singleimplementation. Conversely, various features that are described in thecontext of a single implementation can be implemented in multipleimplementations separately or in any suitable subcombination. Althoughfeatures may be described herein as acting in certain combinations, oneor more features from a claimed combination can, in some cases, beexcised from the combination, and the combination may be claimed as anysubcombination or variation of any subcombination.

While the methods and devices described herein may be susceptible tovarious modifications and alternative forms, specific examples thereofhave been shown in the drawings and are herein described in detail. Itshould be understood, however, that the invention is not to be limitedto the particular forms or methods disclosed, but, to the contrary, theinvention is to cover all modifications, equivalents, and alternativesfalling within the spirit and scope of the various embodiments describedand the appended claims. Further, the disclosure herein of anyparticular feature, aspect, method, property, characteristic, quality,attribute, element, or the like in connection with an embodiment can beused in all other embodiments set forth herein. Any methods disclosedherein need not be performed in the order recited. Depending on theembodiment, one or more acts, events, or functions of any of thealgorithms, methods, or processes described herein can be performed in adifferent sequence, can be added, merged, or left out altogether (e.g.,not all described acts or events are necessary for the practice of thealgorithm). In some embodiments, acts or events can be performedconcurrently, e.g., through multi-threaded processing, interruptprocessing, or multiple processors or processor cores or on otherparallel architectures, rather than sequentially. Further, no element,feature, block, or step, or group of elements, features, blocks, orsteps, are necessary or indispensable to each embodiment. Additionally,all possible combinations, subcombinations, and rearrangements ofsystems, methods, features, elements, modules, blocks, and so forth arewithin the scope of this disclosure. The use of sequential, ortime-ordered language, such as “then,” “next,” “after,” “subsequently,”and the like, unless specifically stated otherwise, or otherwiseunderstood within the context as used, is generally intended tofacilitate the flow of the text and is not intended to limit thesequence of operations performed. Thus, some embodiments may beperformed using the sequence of operations described herein, while otherembodiments may be performed following a different sequence ofoperations.

Moreover, while operations may be depicted in the drawings or describedin the specification in a particular order, such operations need not beperformed in the particular order shown or in sequential order, and alloperations need not be performed, to achieve the desirable results.Other operations that are not depicted or described can be incorporatedin the example methods and processes. For example, one or moreadditional operations can be performed before, after, simultaneously, orbetween any of the described operations. Further, the operations may berearranged or reordered in other implementations. Also, the separationof various system components in the implementations described hereinshould not be understood as requiring such separation in allimplementations, and it should be understood that the describedcomponents and systems can generally be integrated together in a singleproduct or packaged into multiple products. Additionally, otherimplementations are within the scope of this disclosure.

Some embodiments have been described in connection with the accompanyingfigures. Certain figures are drawn and/or shown to scale, but such scaleshould not be limiting, since dimensions and proportions other than whatare shown are contemplated and are within the scope of the embodimentsdisclosed herein. Distances, angles, etc. are merely illustrative and donot necessarily bear an exact relationship to actual dimensions andlayout of the devices illustrated. Components can be added, removed,and/or rearranged. Further, the disclosure herein of any particularfeature, aspect, method, property, characteristic, quality, attribute,element, or the like in connection with various embodiments can be usedin all other embodiments set forth herein. Additionally, any methodsdescribed herein may be practiced using any device suitable forperforming the recited steps.

The methods disclosed herein may include certain actions taken by apractitioner; however, the methods can also include any third-partyinstruction of those actions, either expressly or by implication. Forexample, actions such as “positioning an electrode” include “instructingpositioning of an electrode.”

In summary, various embodiments and examples of systems and methods forinflatable implants, and pressure attenuating inflatable implants, havebeen disclosed. Although the systems and methods for inflatableimplants, and pressure attenuating inflatable implants, have beendisclosed in the context of those embodiments and examples, thisdisclosure extends beyond the specifically disclosed embodiments toother alternative embodiments and/or other uses of the embodiments, aswell as to certain modifications and equivalents thereof. Thisdisclosure expressly contemplates that various features and aspects ofthe disclosed embodiments can be combined with, or substituted for, oneanother. Thus, the scope of this disclosure should not be limited by theparticular disclosed embodiments described herein, but should bedetermined only by a fair reading of the claims that follow.

The ranges disclosed herein also encompass any and all overlap,sub-ranges, and combinations thereof. Language such as “up to,” “atleast,” “greater than,” “less than,” “between,” and the like includesthe number recited. Numbers preceded by a term such as “about” or“approximately” include the recited numbers and should be interpretedbased on the circumstances (e.g., as accurate as reasonably possibleunder the circumstances, for example ±5%, ±10%, ±15%, etc.). Forexample, “about 1 V” includes “1 V.” In addition, it is anticipated thatwith numbers in the description preceded by the term such as “about” or“approximately” these numbers can be claimed with or without the term“about” or “approximately” preceding these numbers. Phrases preceded bya term such as “substantially” include the recited phrase and should beinterpreted based on the circumstances (e.g., as much as reasonablypossible under the circumstances). For example, “substantiallyperpendicular” includes “perpendicular.” Unless stated otherwise, allmeasurements are at standard conditions including temperature andpressure.

1-19. (canceled)
 20. A pressure attenuation device for use in a body,the pressure attenuation device comprising: a balloon comprising anouter wall and defining an interior chamber therein, the balloon beingconfigured to elastically deform and increase in volume by at least 50%but less than 190% when an internal pressure within the balloon isincreased from 2.5 cm H₂O to 90 cm H₂O.
 21. The pressure attenuationdevice of claim 20, wherein the balloon is configured to elasticallydeform and increase in volume by at least 65% but less than 100% when apressure within the balloon is increased from 2.5 cm H₂O to 90 cm H₂O.22. The pressure attenuation device of claim 20 wherein the balloon isconfigured to elastically deform and increase in volume by at least 75%but less than 90% when a pressure within the balloon is increased from2.5 cm H₂O to 90 cm H₂O.
 23. The pressure attenuation device of claim20, wherein the balloon is configured to elastically deform and increasein volume by at least 20% but less than 150% when a pressure within theballoon is increased from 2.5 cm H₂O to 70 cm H₂O.
 24. The pressureattenuation device of claim 20, wherein the balloon is configured toelastically deform and increase in volume by at least 30% but less than100% when a pressure within the balloon is increased from 2.5 cm H₂O to70 cm H₂O.
 25. The pressure attenuation device of claim 20, wherein theballoon is configured to elastically deform and increase in volume by atleast 45% but less than 60% when a pressure within the balloon isincreased from 2.5 cm H₂O to 70 cm H₂O.
 26. The pressure attenuationdevice of claim 20, wherein the balloon is configured to elasticallydeform and increase in volume by at least 10% but less than 45% when apressure within the balloon is increased from 2.5 cm H₂O to 40 cm H₂O.27. The pressure attenuation device of claim 20, wherein the balloon isconfigured to elastically deform and increase in volume by at least 18%but less than 30% when a pressure within the balloon is increased from2.5 cm H₂O to 40 cm H₂O.
 28. The pressure attenuation device of claim20, wherein the balloon is configured to elastically deform and increasein volume by at least 19% but less than 27% when a pressure within theballoon is increased from 2.5 cm H₂O to 40 cm H₂O
 29. The pressureattenuation device of claim 20 comprising a high vapor pressure mediahaving a vapor pressure of between 155 cm H₂O-185 cm H₂O at 37 degreesCelsius.
 30. The pressure attenuation device of claim 20, comprising ahigh vapor pressure media having a vapor pressure of between 155 cmH₂O-165 cm H₂O at 37 degrees Celsius.
 31. The pressure attenuationdevice of claim 29 wherein the high vapor pressure media is positionedwithin the interior chamber.
 32. The pressure attenuation device ofclaim 29, wherein the high vapor pressure media comprises a PFC.
 33. Thepressure attenuation device of claim 20, wherein the balloon elasticallydeforms between internal pressures of 2.5 cm H₂O to 90 cm H₂O for atleast 15 cycles.
 34. The pressure attenuation device of claim 20,wherein the balloon has a natural volume of between 1 and 180 cc. 35.The pressure attenuation device of claim 20 wherein the balloon has aminimum wall thickness of between 0.001 inches and 0.00175 inches. 36.An pressure attenuation device for use in a body, the pressureattenuation device comprising: a balloon comprising an outer wall anddefining an interior chamber therein; and a high vapor pressure media;the balloon being configured to deform elastically at least up to aninternal pressure within the chamber of 90 cm H₂O.
 37. The pressureattenuation device of claim 36 wherein the balloon elastically deformsbetween internal pressures of 2.5 cm H₂O to 90 cm H₂O for at least 15cycles, 25 cycles, 50 cycles or 100 cycles.
 38. The pressure attenuationdevice of claim 37, wherein the balloon is configured to deformelastically at least up to an internal pressure within the chamber of100 cm H₂O.
 39. The pressure attenuation device of claim 38 wherein theballoon elastically deforms between internal pressures of 2.5 cm H₂O to100 cm H₂O for at least 15 cycles, 25 cycles, 50 cycles or 100 cycles.40. The pressure attenuation device of claim 39, wherein the balloon isconfigured to deform elastically at least up to an internal pressurewithin the chamber of 120 cm H₂O.
 41. The pressure attenuation device ofclaim 40 wherein the balloon elastically deforms between internalpressures of 2.5 cm H₂O to 120 cm H₂O for at least 15 cycles.
 42. Thepressure attenuation device of claim 36, wherein the balloon has anatural volume of between 1 and 180 cc.
 43. The pressure attenuationdevice of claim 36, wherein the balloon has a minimum wall thickness ofbetween 0.001 inches-and 0.00175 inches.
 44. The pressure attenuationdevice of claim 43, wherein the high vapor pressure media has a vaporpressure of between 155 cm H₂O-185 cm H₂O at 37 degrees Celsius.
 45. Thepressure attenuation device of claim 44, wherein the high vapor pressuremedia has a vapor pressure of between 155 cm H₂O-165 cm H₂O at 37degrees Celsius.
 46. The pressure attenuation device of claim 45,wherein the high vapor pressure media is positioned within the interiorchamber.
 47. The pressure attenuation device of claim 46, wherein thehigh vapor pressure media comprises a PFC.
 48. The pressure attenuationdevice of claim 47, wherein the high vapor pressure media comprises aliquid at 37 degrees Celsius.
 49. A method of treating urinaryincontinence in a human or animal body comprising implanting a pressureattenuation device comprising a balloon comprising an outer wall anddefining an interior chamber therein, the balloon having a minimum wallthickness of between 0.001 inches and 0.00175 inches, the balloon beingconfigured to elastically deform up to at least to an internal pressureof 90 cm H₂O within a bladder of the human or animal body and inflatingthe pressure attenuation device while in the bladder. 50-51. (canceled)